Radiation systems for radition treatment and imaging

ABSTRACT

A radiation system is provided. The radiation system may include a bore accommodating an object, a rotary ring, a first radiation source and a second radiation source mounted on the rotary ring and a processor. The first radiation source may be configured to emit a first cone beam toward a first region of the object. The second radiation source may be configured to emit a second beam toward a second region of the object, the second region including at least a part of the first region. The processor may be configured to obtain a treatment plan of the object, the treatment plan including parameters associated with radiation segments. The processor may be further configured to control an emission of the first cone beam and/or the second beam based on the parameters associated with the radiation segments to perform a treatment and a 3-D imaging simultaneously.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a Continuation of U.S. application Ser. No.16/286,494, filed on Feb. 26, 2019, which is a Continuation ofInternational Application No. PCT/CN2018/085266, filed on May 2, 2018,the contents of which is incorporated herein by reference.

TECHNICAL FIELD

The present disclosure generally relates to radiation systems, and morespecifically relates to radiation delivery devices including a treatmentradiation source and an imaging radiation source mounted on a rotaryring.

BACKGROUND

Radiotherapy has been widely employed in cancer treatment in whichionizing radiation is guided towards a tumor region. Considerations ofradiotherapy include that the tumor receives sufficient radiation, whilethe damage to an organ at risk (OAR) is minimized as much as possibleduring the radiotherapy. The tumor and/or the OAR may be in motion dueto a physiological motion (e.g., respiratory motion, cardiac motion,muscle contraction, and relaxation) of the object under the treatment.The tumor region may change with such motion of the object. However,under traditional radiotherapy systems, the area where the radiationimpinging upon an object is often fixed, and the change of the tumorregion due to the motion of the object may cause more damage to OARs andthe radiation efficacy to deteriorate. Thus, it is desirable to design asystem capable of detecting the motion of the tumor and adjusting theradiation to the tumor region accordingly.

SUMMARY

According to an aspect of the present disclosure, a radiation system isprovided. The radiation system may include: a bore configured toaccommodate an object, a rotary ring, a first radiation source mountedon the rotary ring, a second radiation source mounted on the rotary ringand a processor. The first radiation source may be configured to emit afirst cone beam toward a first region of the object, with a 2-Dcollimator positioned between a center of the bore and the firstradiation source to form at least one aperture, the aperture modifying ashape of the first cone beam. The second radiation source may beconfigured to emit a second beam toward a second region of the object,the second region including at least a part of the first region. Theprocessor may be configured to cause the radiation system to obtain atreatment plan of the object, the treatment plan including parametersassociated with one or more radiation segments. The processor may befurther configured to cause the radiation system to cause the rotaryring to rotate around the object in one direction continuously for atleast two full rotations. The processor may be further configured tocause the radiation system to adjust the at least one aperture of the2-D collimator based on the parameters associated with the one or moreradiation segments. The processor may be further configured to cause theradiation system to control an emission of at least one of the firstcone beam or the second beam based on the parameters associated with theone or more radiation segments to perform a treatment and a 3-D imagingsimultaneously.

In some embodiments, the 2-D collimator may include a multi-leafcollimator (MLC) including a plurality of leaves to form the aperture.

In some embodiments, when the rotary ring rotates, an angular offsetbetween the first radiation source and the second radiation source in aplane of the rotation of the rotary ring remains unchanged.

In some embodiments, the parameters associated with the one or moreradiation segments include at least one of a desired segment shape, adesired segment MU value, a desired segment MU rate, a desired segmentangle range, or a desired relative position of the object relative tothe rotary ring.

In some embodiments, the radiation system further includes a radiationdetector configured to detect radiation impinging on the radiationdetector. The processor is further configured to cause the radiationsystem to obtain treatment planning image data of the object associatedwith the treatment plan. The processor is further configured to causethe radiation system to generate a radiograph or CT image data based onthe detected radiation by the radiation detector, the detected radiationbeing associated with at least one of the first cone beam or the secondbeam. The processor is further configured to cause the radiation systemto compare the generated radiograph or CT image data with the treatmentplanning image data. The processor is further configured to cause theradiation system to determine whether the treatment plan needs to beadjusted based on a result of the comparison between the generatedradiograph or CT image data and the treatment planning image data. Theprocessor is further configured to cause the radiation system to adjust,based on a result of the determination that the treatment plan needs tobe adjusted, at least one of the parameters associated with the one ormore radiation segments.

In some embodiments, the radiograph or the CT image data is obtainedduring a part of a rotation of the rotary ring.

In some embodiments, the radiation system may further include a bedconfigured to support the object, wherein the processor is furtherconfigured to cause the radiation system to adjust a position of the bedbased on a desired position of the object with respect to the rotaryring.

In some embodiments, the processor is further configured to cause theradiation system to obtain respiration information of the object. Theprocessor is further configured to cause the radiation system todetermine a rotation parameter of the rotary ring based on therespiration information of the object. The processor is furtherconfigured to cause the radiation system to control a rotation of therotary ring based, at least in part, on the determined rotationparameter.

In some embodiments, the rotation parameter includes a rotation speed.

In some embodiments, within a period that the rotary ring rotates a fullrotation, the first radiation source emits the first cone beam and thesecond radiation source emits a second beam.

In some embodiments, a period that the rotary ring rotates a fullrotation is less than 30 seconds.

In some embodiments, the radiation system may further include aradiation detector configured to detect radiation impinging upon thedetector. The processor is further configured to cause the radiationsystem to cause the rotary ring to rotate a first full rotation and asecond full rotation, the second full rotation being after the firstfull rotation. The processor is further configured to cause theradiation system to adjust, based on radiation detected by the radiationdetector in the first full rotation, parameters associated with theradiation segments at which the first radiation source emits a firstcone beam in the second full rotation. The processor is furtherconfigured to cause the radiation system to control an emission of thefirst cone beam based on the adjusted parameters associated with theradiation segments.

In some embodiments, the radiation system may further include aradiation detector configured to detect radiation impinging upon thedetector. The processor is further configured to cause the radiationsystem to cause the rotary ring to rotate. The processor is furtherconfigured to cause the radiation system to adjust, based on radiationdetected by the radiation detector in the present rotation, parametersassociated with radiation segments that follow the radiation detectionby the radiation detector in the present rotation. The processor isfurther configured to cause the radiation system to control an emissionof the first cone beam at the radiation segments that follow theradiation detection by the radiation detector based on the adjustedparameters associated with the radiation segments that follow theradiation detection by the radiation detector in the present rotation.

In some embodiments, a rotation of the rotary ring is driven via atleast one of a slip ring, a gear, a reel, or a rotation shaft.

In some embodiments, the radiation system may further include a movementrestriction component configured to limit a movement of the rotary ring.

In some embodiments, a cone angle of the second beam is greater than orequal to a cone angle of the first cone beam.

In some embodiments, the radiation system may further include a CTdetector configured to detect radiation emitted by the second radiationsource after attenuation by the object.

In some embodiments, the radiation system may further include a flatpanel detector configured to detect radiation emitted by the firstradiation source after attenuation by the object.

In some embodiments, the radiation system may further include a bedconfigured to support the object and move in a first direction. Theprocessor is further configured to cause the radiation system to movethe first radiation source in the first direction.

In some embodiments, the first radiation source moves at a speed equalto a speed of the bed.

In some embodiments, the radiation system may further include a bedconfigured to support the object and move in a first direction. Theprocessor is further configured to cause the radiation system to disposethe 2-D collimator of the first radiation source to move in the firstdirection.

In some embodiments, the 2-D collimator of the first radiation sourcemoves at a speed equal to a moving speed of the bed.

In some embodiments, to perform the 3-D imaging, the processor isconfigured to cause the system to generate a 3-D image based on areceived radiation associated with the first cone beam and the secondbeam.

In some embodiments, to perform the 3-D imaging, the processor isconfigured to cause the system to generate a 3-D image based on areceived radiation associated with the first cone beam and the secondbeam emitted in a same full rotation.

In some embodiments, to perform the 3-D imaging, the processor isconfigured to cause the system to generate a 3-D image based on areceived radiation associated with the first cone beam and the secondbeam emitted in a same fraction of a full rotation.

According to another aspect of the present disclosure, a radiationsystem is provided. The radiation system may include a bore configuredto accommodate an object, a rotary ring, a first radiation sourcemounted on the rotary ring, a second radiation source mounted on therotary ring, and a processor. The first radiation source may beconfigured to emit a first cone beam toward a first region of theobject, with a 2-D collimator positioned between a center of the boreand the first radiation source to form at least one aperture, theaperture modifying a shape of the first cone beam. The second radiationsource may be configured to emit a second beam toward a second region ofthe object, the second region including at least a part of the firstregion. The processor may be configured to cause the radiation system toobtain a treatment plan of the object, the treatment plan includingparameters associated with one or more radiation segments. The processormay be further configured to adjust a position of the object relative tothe first cone beam based on the parameters associated with the one ormore radiation segments. The processor may be further configured tocontrol an emission of at least one of the first cone beam or the secondbeam based on the parameters associated with the one or more radiationsegments to perform a treatment and a 3-D imaging simultaneously.

In some embodiments, images generated by the second radiation source areused to modify the position of the object with respect to the firstradiation source such that target tissue in the first region is centeredat an isocenter of the radiation system.

In some embodiments, the target tissue in the first region ispartitioned into subvolumes, the subvolumes being treated seriallyduring different rotation angles of the rotary ring. The processor isfurther configured to cause the radiation system to adjust a position ofat least one of the subvolumes such that a center of the at least one ofthe subvolumes substantially overlaps with the isocenter of theradiation system.

In some embodiments, respiration information is used to modify theposition of the object with respect to the first radiation source suchthat target tissue in the first region is substantially centered at anisocenter of the radiation system.

In some embodiments. the target tissue in the first region ispartitioned into subvolumes, the subvolumes being treated seriallyduring different rotation angles of the rotary ring. The processor isfurther configured to cause the radiation system to adjust a position ofat least one of the subvolumes such that a center of the at least one ofthe subvolumes substantially overlaps with the isocenter of theradiation system.

In some embodiments, to perform the 3-D imaging, the processor isconfigured to cause the system to generate a 3-D image based on areceived radiation associated with the first cone beam and the secondbeam.

In some embodiments, to perform the 3-D imaging, the processor isconfigured to cause the system to generate a 3-D image based on areceived radiation associated with the first cone beam and the secondbeam emitted in a same full rotation.

In some embodiments, to perform the 3-D imaging, the processor isconfigured to cause the system to generate a 3-D image based on areceived radiation associated with the first cone beam and the secondbeam emitted in a same fraction of a full rotation.

In some embodiments, electric power may be transferred to the firstradiation source and the second radiation source via a slip ring.

In some embodiments, a detector may be paired with the second radiationsource, configured to detect radiation associated with the second beam.Control and imaging data may be transferred to and from the pairedsecond radiation source and detector via a slip ring.

BRIEF DESCRIPTION OF THE DRAWINGS

The present disclosure is further described in terms of exemplaryembodiments. These exemplary embodiments are described in detail withreference to the drawings. These embodiments are non-limiting exemplaryembodiments, in which like reference numerals represent similarstructures throughout the several views of the drawings, and wherein:

FIG. 1 is a schematic diagram illustrating an exemplary radiation systemaccording to some embodiments of the present disclosure;

FIG. 2 is a schematic diagram illustrating hardware and/or softwarecomponents of an exemplary computing device according to someembodiments of the present disclosure;

FIG. 3 is a schematic diagram illustrating hardware and/or softwarecomponents of an exemplary mobile device according to some embodimentsof the present disclosure;

FIG. 4 is a schematic diagram illustrating an exemplary radiationdelivery device according to some embodiments of the present disclosure;

FIG. 5 is a schematic diagram illustrating an exemplary slip ringaccording to some embodiments of the present disclosure;

FIG. 6 is a schematic diagram illustrating an exemplary connection of arotary ring and a slip ring according to some embodiments of the presentdisclosure;

FIG. 7A and FIG. 7B are schematic diagrams illustrating differentconfigurations of an exemplary radiation delivery device according tosome embodiments of the present disclosure;

FIG. 8 is a schematic diagram illustrating an exemplary multi-leafcollimator (MLC) according to some embodiments of the presentdisclosure;

FIG. 9 is schematic diagram illustrating a shape of an exemplaryaperture formed by an MLC and a corresponding treatment region;

FIG. 10 is a block diagram illustrating an exemplary processing deviceaccording to some embodiments of the present disclosure;

FIG. 11 is a schematic diagram illustrating an exemplary process of CTscans and RT treatments in different rotations according to someembodiments of the present disclosure;

FIG. 12 is a flowchart illustrating an exemplary process for controllinga rotation of the rotary ring based on respiration information of anobject;

FIG. 13 is a flowchart illustrating an exemplary process for controllingemissions of beams from a first radiation source and a second radiationsource;

FIG. 14 is a flowchart illustrating an exemplary process for adjustingthe treatment plan based on radiation detected by a radiation detector;and

FIG. 15 is a flowchart illustrating an exemplary process for adjustingone or more components of the radiation system based on the adjustedtreatment plan.

DETAILED DESCRIPTION

In the following detailed description, numerous specific details are setforth by way of examples in order to provide a thorough understanding ofthe relevant disclosure. However, it should be apparent to those skilledin the art that the present disclosure may be practiced without suchdetails. In other instances, well-known methods, procedures, systems,components, and/or circuitry have been described at a relativelyhigh-level, without detail, in order to avoid unnecessarily obscuringaspects of the present disclosure. Various modifications to thedisclosed embodiments will be readily apparent to those skilled in theart, and the general principles defined herein may be applied to otherembodiments and applications without departing from the spirit and scopeof the present disclosure. Thus, the present disclosure is not limitedto the embodiments shown, but to be accorded the widest scope consistentwith the claims.

The terminology used herein is for the purpose of describing particularexample embodiments only and is not intended to be limiting. As usedherein, the singular forms “a,” “an,” and “the” may be intended toinclude the plural forms as well, unless the context clearly indicatesotherwise. It will be further understood that the terms “comprise,”“comprises,” and/or “comprising,” “include,” “includes,” and/or“including,” when used in this specification, specify the presence ofstated features, integers, steps, operations, elements, and/orcomponents, but do not preclude the presence or addition of one or moreother features, integers, steps, operations, elements, components,and/or groups thereof. It will be understood that the term “object” and“subject” may be used interchangably as a reference to a thing thatundergoes a treatment and/or an imaging in a radiation system of thepresent disclosure.

It will be understood that the term “system,” “engine,” “unit,”“module,” and/or “block” used herein are one method to distinguishdifferent components, elements, parts, section or assembly of differentlevel in ascending order. However, the terms may be displaced by anotherexpression if they achieve the same purpose.

Generally, the word “module,” “unit,” or “block,” as used herein, refersto logic embodied in hardware or firmware, or to a collection ofsoftware instructions. A module, a unit, or a block described herein maybe implemented as software and/or hardware and may be stored in any typeof non-transitory computer-readable medium or another storage device. Insome embodiments, a software module/unit/block may be compiled andlinked into an executable program. It will be appreciated that softwaremodules can be callable from other modules/units/blocks or themselves,and/or may be invoked in response to detected events or interrupts.Software modules/units/blocks configured for execution on computingdevices (e.g., processor 210 as illustrated in FIG. 2) may be providedon a computer-readable medium, such as a compact disc, a digital videodisc, a flash drive, a magnetic disc, or any other tangible medium, oras a digital download (and can be originally stored in a compressed orinstallable format that needs installation, decompression, or decryptionprior to execution). Such software code may be stored, partially orfully, on a storage device of the executing computing device, forexecution by the computing device. Software instructions may be embeddedin firmware, such as an EPROM. It will be further appreciated thathardware modules/units/blocks may be included in connected logiccomponents, such as gates and flip-flops, and/or can be included ofprogrammable units, such as programmable gate arrays or processors. Themodules/units/blocks or computing device functionality described hereinmay be implemented as software modules/units/blocks but may berepresented in hardware or firmware. In general, themodules/units/blocks described herein refer to logicalmodules/units/blocks that may be combined with othermodules/units/blocks or divided into sub-modules/sub-units/sub-blocksdespite their physical organization or storage. The description mayapply to a system, an engine, or a portion thereof.

It will be understood that when a unit, engine, module or block isreferred to as being “on,” “connected to,” or “coupled to,” anotherunit, engine, module, or block, it may be directly on, connected orcoupled to, or communicate with the other unit, engine, module, orblock, or an intervening unit, engine, module, or block may be present,unless the context clearly indicates otherwise. As used herein, the term“and/or” includes any and all combinations of one or more of theassociated listed items.

These and other features, and characteristics of the present disclosure,as well as the methods of operation and functions of the relatedelements of structure and the combination of parts and economies ofmanufacture, may become more apparent upon consideration of thefollowing description with reference to the accompanying drawings, allof which form a part of this disclosure. It is to be expresslyunderstood, however, that the drawings are for the purpose ofillustration and description only and are not intended to limit thescope of the present disclosure. It is understood that the drawings arenot to scale.

The flowcharts used in the present disclosure illustrate operations thatsystems implement according to some embodiments of the presentdisclosure. It is to be expressly understood, the operations of theflowcharts may be implemented not in order. Conversely, the operationsmay be implemented in inverted order, or simultaneously. Moreover, oneor more other operations may be added to the flowcharts. One or moreoperations may be removed from the flowcharts.

An aspect of the present disclosure relates to a radiation deliverydevice for imaging an object (also referred to as a subject) duringradiotherapy. The radiation delivery device disclosed in the presentdisclosure includes an imaging radiation source and a treatmentradiation source both mounted on a rotary ring. The rotary ring mayrotate around the object. With the radiation delivery device, the objectmay be imaged and treated in a rotation of the rotary ring. Thetreatment in a rotation of the rotary ring may depend on the image datagenerated according to a preceding rotation. A treatment plan may beused to control the radiation delivery device. The treatment plan may beadjusted based on the image data and the original treatment plan.

FIG. 1 is a schematic diagram illustrating an exemplary radiation system100 according to some embodiments of the present disclosure. Theradiation system 100 may include a radiation delivery device 110, anetwork 120, one or more terminals 130, a processing device 140, and astorage device 150.

The radiation delivery device 110 may include a first radiation source113 and a second radiation source 111. The examples of the firstradiation source 113 may be found elsewhere in this disclosure (e.g.,treatment radiation source 430 illustrated in FIG. 4, treatmentradiation source 730 illustrated in FIG. 7). The examples of the secondradiation source 111 may be found elsewhere in this disclosure (e.g.,treatment radiation source 410 illustrated in FIG. 4, treatmentradiation source 710 illustrated in FIG. 7). The first radiation source113 may emit a first beam (also referred to as a first cone beam) towarda first region of an object (e.g., a patient or a portion thereof). Thesecond radiation source 111 may emit a second beam toward a secondregion of the object. The second region may overlap with the firstregion (e.g., the second region may include at least part of the firstregion). In some embodiments, the first beam and the second beam mayeach include at least one radiation ray. The radiation ray may includebut not limited to X-rays, α-rays, β-rays, γ-rays, heavy ions, etc.Merely by way of example, the first radiation source may be a treatmentradiation source, and the first region may correspond to a treatmentregion (e.g., a tumor). The second radiation source may be an imagingradiation source, and the second region may correspond to an imagingregion including at least part of the treatment region. The intensity ofthe first beam may be the same as or different from the intensity of thesecond beam. For example, the energy of the first beam may be severalmegavolts (MV), this energy being greater than that of the second beam,which may be several kilovolts (kV).

The intensity of the radiation source (e.g., the first radiation source113 and the second radiation source 111) can be changed in various ways.In a typical configuration, a linear accelerator associated with theradiation source (e.g., an accelerator that accelerates an electrontowards a target to generate X-rays) may be operated in a pulsed mode,where radiation is produced in a very short pulse [each pulse lastingfor example 3 microseconds], while the intensity remains constant duringthe pulse. For example, in order to achieve a change of (average)intensity, the duration of the pulse or the frequency of the pulses maybe adjusted, such that when averaged over a period of time (for example100 ms to 1 second), the intensity of the beam is changed. In typicalembodiments, this averaged intensity is referred to as the “dose rate”or “output rate” of the linear accelerator and is typically expressed inMonitor Units (MU) per minute. An MU is a measure of machine radiationoutput. It is typically calibrated to a dose absorbed in a standardizedphantom at a standardized position, under standardized conditions ofirradiation. An MU rate is the number of MU that are produced per unittime. It is common to use the terms MU rate and dose rateinterchangeably. However, in the strict sense, dose rate depends notonly on the machine radiation output, but also the properties of theobject to which radiation is imparted. In radiation therapy, the dose tobe absorbed by a target tissue is prescribed. The radiation system 100may produce a sequence of machine parameters to achieve the prescribeddose to be absorbed in the target tissue.

Thus, in a typical treatment plan, one of the main parameters which isoptimized is the dose to be absorbed by tissues. Dose is linearlyproportional to MU, as long as the exposed object and irradiationconditions do not change. As such, the dose rate will express the speedwith which a certain dose is delivered. If all other parameters(including, but not limited to, beam shape or source position) remainconstant, the dose rate itself is not very significant, since thespatial distribution of the dose in the target will not be affected bydifferent dose rates. If, however, during the delivery, any otherparameter such as the beam shape of the position of the source ismodified, a change in dose rate will affect how the dose is distributedover the target volume. Under such conditions, the dose rate itself mayalso need to be optimized in order to achieve the correct dosedistribution.

In some embodiments, the radiation delivery device 110 may furtherinclude a radiation detector 112 placed opposite to the second radiationsource 111. In some embodiments, the radiation detector 112 may bemounted on a rotary ring 114. The radiation detector 112 may beconfigured to detect radiation. The second beam emitted from the secondradiation source 111 may transmit through (or be absorbed by) the objectand attenuate when passing through the object. The radiation detector112 may detect and/or receive radiation associated with at least aportion of the attenuated or scattered second beam. The radiation system100 (e.g., a processing device 140) may generate radiographs and CTimages based on the received portion of the attenuated second beam. Insome embodiments, the radiographs or the CT images may be obtainedduring a full rotation or a part of a rotation of the rotary ring (e.g.,½ rotation, ¼ rotation, 1/10^(th) rotation, 1/20^(th) rotation,1/100^(th) rotation, etc.) The first radiation source 113, the secondradiation source 111 and the radiation detector 112 may be mounted on arotary ring 114. The rotary ring 114 may rotate around the object. Theexamples of the rotary ring 114 may be found elsewhere in thisdisclosure (e.g., rotary ring 440 illustrated in FIG. 4, rotary ring 630illustrated in FIG. 6, rotary ring 740 illustrated in FIG. 7). Theangular offset between first radiation source 113 and the secondradiation source 111 (and/or the radiation detector 112) in a plane ofthe rotation of the rotary ring 114 may remain unchanged during therotation of the rotary ring 114. In some embodiments, the radiationsystem 100 may include a gantry 116 to accommodate a bore 117 and a bed115. Since the radiation system 100 is a combined therapy-imagingsystem, the bed 115 may be a scanning bed or a treatment couch. Therotary ring 114 may be rotatably connected to the gantry (e.g., therotary ring 114 may rotate in X-Y plane but may not move in Z-directionwhen connected to the gantry 116). The bed 115 may be configured tosupport and/or transport the object (e.g., a patient) to the gantry 116to be imaged and/or undergo radiotherapy.

It should be noted that the above descriptions of the radiation deliverydevice 110 are merely provided for the purposes of illustration, and notintended to limit the scope of the present disclosure. For personshaving ordinary skill in the art, multiple variations and modificationsmay be made under the teachings of the present disclosure. However,those variations and modifications do not depart from the scope of thepresent disclosure. For example, the first radiation source 113 and thesecond radiation source 111 may both be treatment radiation sources. Asanother example, the first radiation source 113 and the second radiationsource 111 may both be imaging radiation sources. Merely by way ofexample, a radiation detector may be mounted opposite to the firstradiation source 113 on the rotary ring 114 configured to detect atleast a portion of the first beam emitted from the first radiationsource 113 (a portion of which may be attenuated when reaching theradiation detector). In some embodiments, the second radiation source111 may be replaced by any other type of imaging device such as acomputed tomography (CT) device, a magnetic resonance imaging (MRI)device, a positron emission tomography (PET) device, a single photonemission computed tomography (SPECT) device, or the like, or acombination thereof. More descriptions of the radiation delivery device110 may be found elsewhere in the present disclosure (e.g., FIG. 4 andthe descriptions thereof).

The network 120 may include any suitable network that can facilitate theexchange of information and/or data for the radiation system 100. Insome embodiments, one or more components of the radiation system 100(e.g., the radiation delivery device 110, the terminal(s) 130, theprocessing device 140, or the storage device 150) may communicateinformation and/or data with one or more other components of theradiation system 100 via the network 120. For example, the processingdevice 140 may obtain data corresponding to radiation signals from theradiation delivery device 110 via the network 120. As another example,the processing device 140 may obtain user instructions from theterminal(s) 130 via the network 120. In some embodiments, the network120 may be any type of wired or wireless network, or a combinationthereof. The network 120 may be and/or include a public network (e.g.,the Internet), a private network (e.g., a local area network (LAN), awide area network (WAN)), etc.), a wired network (e.g., an Ethernetnetwork), a wireless network (e.g., an 802.11 network, a Wi-Fi network,etc.), a cellular network (e.g., a Long Term Evolution (LTE) network), aframe relay network, a virtual private network (“VPN”), a satellitenetwork, a telephone network, routers, hubs, switches, server computers,and/or a combination thereof. Merely by way of example, the network 120may include a cable network, a wireline network, a fiber-optic network,a telecommunications network, an intranet, a wireless local area network(WLAN), a metropolitan area network (MAN), a public telephone switchednetwork (PSTN), a Bluetooth™ network, a ZigBee™ network, a near fieldcommunication (NFC) network, or the like, or a combination thereof. Insome embodiments, the network 120 may include one or more network accesspoints. For example, the network 120 may include wired and/or wirelessnetwork access points such as base stations and/or internet exchangepoints through which one or more components of the radiation system 100may be connected to the network 120 to exchange data and/or information.

The terminal(s) 130 may include a mobile device 131, a tablet computer132, a laptop computer 133, or the like, or a combination thereof. Insome embodiments, the mobile device 131 may include a smart home device,a wearable device, a smart mobile device, a virtual reality device, anaugmented reality device, or the like, or a combination thereof. In someembodiments, the smart home device may include a smart lighting device,a control device of an intelligent electrical device, a smart monitoringdevice, a smart television, a smart video camera, an interphone, or thelike, or a combination thereof. In some embodiments, the wearable devicemay include a smart bracelet, smart footgear, a pair of smart glasses, asmart helmet, a smartwatch, smart clothing, a smart backpack, a smartaccessory, or the like, or a combination thereof. In some embodiments,the smart mobile device may include a smartphone, a personal digitalassistant (PDA), a gaming device, a navigation device, a point of sale(POS) device, or the like, or a combination thereof. In someembodiments, the virtual reality device and/or the augmented realitydevice may include a virtual reality helmet, a virtual reality glass, avirtual reality patch, an augmented reality helmet, an augmented realityglass, an augmented reality patch, or the like, or a combinationthereof. For example, the virtual reality device and/or the augmentedreality device may include a Google Glass, an Oculus Rift, a Hololens, aGear VR, etc. In some embodiments, the terminal(s) 130 may remotelyoperate the radiation delivery device 110. In some embodiments, theterminal(s) 130 may operate the radiation delivery device 110 via awireless connection. In some embodiments, the terminal(s) 130 mayreceive information and/or instructions inputted by a user, and send thereceived information and/or instructions to the radiation deliverydevice 110 or the processing device 140 via the network 120. In someembodiments, the terminal(s) 130 may receive data and/or informationfrom the processing device 140. In some embodiments, the terminal(s) 130may be part of the processing device 140. In some embodiments, theterminal(s) 130 may be omitted.

The processing device 140 may process data and/or information obtainedfrom the radiation delivery device 110, the terminal(s) 130, and/or thestorage device 150. For example, the processing device 140 may processdata corresponding to radiation signals of one or more detectorsobtained from the radiation delivery device 110 and reconstruct an imageof the object. In some embodiments, the reconstructed image may betransmitted to the terminal(s) 130 and displayed on one or more displaydevices in the terminal(s) 130. The processing device 140 may obtain atreatment plan from the terminal (s), and/or the storage device 150 viathe network 120. The treatment plan may correspond to a certainarrangement of the radiation delivery device 110 or components thereof.The processing device 140 may further adjust the treatment plan based ondata and/or information received from the radiation delivery device 110and may control the radiation delivery device 110 based on the adjustedtreatment plan. In some embodiments, the processing device 140 may be asingle server or a server group. The server group may be centralized ordistributed. In some embodiments, the processing device 140 may be localor remote. For example, the processing device 140 may access informationand/or data stored in the radiation delivery device 110, the terminal(s)130, and/or the storage device 150 via the network 120. As anotherexample, the processing device 140 may be directly connected to theradiation delivery device 110, the terminal(s) 130, and/or the storagedevice 150 to access stored information and/or data. As a furtherexample, the processing device 140 may be integrated into the radiationdelivery device 110. In some embodiments, the processing device 140 maybe implemented on a cloud platform. Merely by way of example, the cloudplatform may include a private cloud, a public cloud, a hybrid cloud, acommunity cloud, a distributed cloud, an inter-cloud, a multi-cloud, orthe like, or a combination thereof. In some embodiments, the processingdevice 140 may be implemented on a computing device 200 having one ormore components illustrated in FIG. 2 in the present disclosure.

The storage device 150 may store data and/or instructions. In someembodiments, the storage device 150 may store data obtained from theterminal(s) 130 and/or the processing device 140. For example, thestorage device 150 may store a treatment plan and/or an adjustedtreatment plan. In some embodiments, the storage device 150 may storedata and/or instructions that the processing device 140 may execute oruse to perform exemplary methods described in the present disclosure. Insome embodiments, the storage device 150 may include a mass storagedevice, a removable storage device, a volatile read-and-write memory, aread-only memory (ROM), or the like, or a combination thereof. Exemplarymass storage may include a magnetic disk, an optical disk, a solid-statedrive, etc. Exemplary removable storage may include a flash drive, afloppy disk, an optical disk, a memory card, a zip disk, a magnetictape, etc. Exemplary volatile read-and-write memory may include a randomaccess memory (RAM). Exemplary RAM may include a dynamic RAM (DRAM), adouble date rate synchronous dynamic RAM (DDR SDRAM), a static RAM(SRAM), a thyristor RAM (T-RAM), and a zero-capacitor RAM (Z-RAM), etc.Exemplary ROM may include a mask ROM (MROM), a programmable ROM (PROM),an erasable programmable ROM (PEROM), an electrically erasableprogrammable ROM (EEPROM), a compact disk ROM (CD-ROM), and a digitalversatile disk ROM, etc. In some embodiments, the storage device 150 maybe implemented on a cloud platform. Merely by way of example, the cloudplatform may include a private cloud, a public cloud, a hybrid cloud, acommunity cloud, a distributed cloud, an inter-cloud, a multi-cloud, orthe like, or a combination thereof.

In some embodiments, the storage device 150 may be connected to thenetwork 120 to communicate with one or more components of the radiationsystem 100 (e.g., the processing device 140, the terminal(s) 130, etc.).One or more components of the radiation system 100 may access the dataor instructions stored in the storage device 150 via the network 120. Insome embodiments, the storage device 150 may be directly connected to orcommunicate with one or more components of the radiation system 100(e.g., the processing device 140, the terminal(s) 130, etc.). In someembodiments, the storage device 150 may be part of the processing device140.

FIG. 2 is a schematic diagram illustrating hardware and/or softwarecomponents of an exemplary computing device 200 on which the processingdevice 140 may be implemented according to some embodiments of thepresent disclosure. As illustrated in FIG. 2, the computing device 200may include a processor 210, a storage 220, an input/output (I/O) 230,and a communication port 240.

The processor 210 may execute computer instructions (program code) andperform functions of the processing device 140 in accordance withtechniques described herein. The computer instructions may include, forexample, routines, programs, objects, components, signals, datastructures, procedures, modules, and functions, which perform particularfunctions described herein. For example, the processor 210 may processdata obtained from the radiation delivery device 110, the terminal(s)130, the storage device 150, and/or any other component of the radiationsystem 100. In some embodiments, the processor 210 may performinstructions obtained from the terminal(s) 130. In some embodiments, theprocessor 210 may include one or more hardware processors, such as amicrocontroller, a microprocessor, a reduced instruction set computer(RISC), an application specific integrated circuits (ASICs), anapplication-specific instruction-set processor (ASIP), a centralprocessing unit (CPU), a graphics processing unit (GPU), a physicsprocessing unit (PPU), a microcontroller unit, a digital signalprocessor (DSP), a field programmable gate array (FPGA), an advancedRISC machine (ARM), a programmable logic device (PLD), any circuit orprocessor capable of executing one or more functions, or the like, or acombinations thereof. Merely for illustration, only one processor isdescribed in the computing device 200. However, it should be noted thatthe computing device 200 in the present disclosure may also includemultiple processors. Thus operations and/or method steps that areperformed by one processor as described in the present disclosure mayalso be jointly or separately performed by the multiple processors. Forexample, if in the present disclosure the processor of the computingdevice 200 executes both process A and process B, it should beunderstood that process A and process B may also be performed by two ormore different processors jointly or separately in the computing device200 (e.g., a first processor executes process A and a second processorexecutes process B, or the first and second processors jointly executeprocesses A and B).

The storage 220 may store data/information obtained from the radiationdelivery device 110, the terminal 130, the storage device 150, or anyother component of the radiation system 100. In some embodiments, thestorage 220 may include a mass storage device, a removable storagedevice, a volatile read-and-write memory, a read-only memory (ROM), orthe like, or a combination thereof. For example, the mass storage mayinclude a magnetic disk, an optical disk, a solid-state drive, etc. Theremovable storage may include a flash drive, a floppy disk, an opticaldisk, a memory card, a zip disk, a magnetic tape, etc. The volatileread-and-write memory may include a random access memory (RAM). The RAMmay include a dynamic RAM (DRAM), a double date rate synchronous dynamicRAM (DDR SDRAM), a static RAM (SRAM), a thyristor RAM (T-RAM), and azero-capacitor RAM (Z-RAM), etc. The ROM may include a mask ROM (MROM),a programmable ROM (PROM), an erasable programmable ROM (PEROM), anelectrically erasable programmable ROM (EEPROM), a compact disk ROM(CD-ROM), and a digital versatile disk ROM, etc. In some embodiments,the storage 220 may store one or more programs and/or instructions toperform exemplary methods described in the present disclosure. Forexample, the storage 220 may store a program for the processing device140 for reducing or removing one or more artifacts in an image.

The I/O 230 may input or output signals, data, and/or information. Insome embodiments, the I/O 230 may enable user interaction with theprocessing device 140. In some embodiments, the I/O 230 may include aninput device and an output device. Exemplary input devices may include akeyboard, a mouse, a touch screen, a microphone, or the like, or acombination thereof. Exemplary output devices may include a displaydevice, a loudspeaker, a printer, a projector, or the like, or acombination thereof. Exemplary display devices may include a liquidcrystal display (LCD), a light-emitting diode (LED)-based display, aflat panel display, a curved screen, a television device, a cathode raytube (CRT), or the like, or a combination thereof.

The communication port 240 may be connected to a network (e.g., thenetwork 120) to facilitate data communications. The communication port240 may establish connections between the processing device 140 and theradiation delivery device 110, the terminal 130, or the storage device150. The connection may be a wired connection, a wireless connection, orcombination of both that enables data transmission and reception. Thewired connection may include an electrical cable, an optical cable, atelephone wire, or the like, or a combination thereof. The wirelessconnection may include Bluetooth, Wi-Fi, WiMax, WLAN, ZigBee, mobilenetwork (e.g., 3G, 4G, 5G, etc.), or the like, or a combination thereof.In some embodiments, the communication port 240 may be a standardizedcommunication port, such as RS232, RS485, etc. In some embodiments, thecommunication port 240 may be a specially designed communication port.For example, the communication port 240 may be designed in accordancewith the digital imaging and communications in medicine (DICOM)protocol.

FIG. 3 is a schematic diagram illustrating hardware and/or softwarecomponents of an exemplary mobile device 300 according to someembodiments of the present disclosure. As illustrated in FIG. 3, themobile device 300 may include a communication platform 310, a display320, a graphics processing unit (GPU) 330, a central processing unit(CPU) 340, an I/O 350, a memory 360, and a storage 390. In someembodiments, any other suitable component, including but not limited toa system bus or a controller (not shown), may also be included in themobile device 300. In some embodiments, a mobile operating system 370(e.g., iOS, Android, Windows Phone, etc.) and one or more applications380 may be loaded into the memory 360 from the storage 390 in order tobe executed by the CPU 340. The applications 380 may include a browseror any other suitable mobile apps for receiving and renderinginformation relating to image processing or other information from theprocessing device 140. User interactions with the information stream maybe achieved via the I/O 350 and provided to the processing device 140and/or other components of the radiation system 100 via the network 120.

To implement various modules, units, and their functionalities describedin the present disclosure, computer hardware platforms may be used asthe hardware platform(s) for one or more of the elements describedherein. The hardware elements, operating systems and programminglanguages of such computers are conventional in nature, and it ispresumed that those skilled in the art are adequately familiar therewithto adapt those technologies to radiation systems for treatment andimaging as described herein. A computer with user interface elements maybe used to implement a personal computer (PC) or other type of workstation or terminal device, although a computer may also act as a serverif appropriately programmed. It is believed that those skilled in theart are familiar with the structure, programming and general operationof such computer equipment and as a result, the drawings should beself-explanatory.

FIG. 4 is a schematic diagram illustrating an exemplary radiationdelivery device according to some embodiments of the present disclosure.As shown in FIG. 4, the radiation delivery device 400 may include atreatment radiation source 430 (also referred to as a first radiationsource), a multi-leaf collimator (MLC) 450, an imaging radiation source410 (also referred to as a second radiation source), and a radiationdetector 420. The MLC may contain leaves that move continuously orassume discrete positions. The MLC may contain leaves that are “binary”in that a leaf may assume only closed (radiation-attenuating) and open(radiation-transmitting) states. The radiation delivery device 400 maybe an exemplary embodiment of the radiation delivery device 110 butshall not be considered as the only possible configuration of theradiation delivery device 110. People having ordinary skill in the artmay, under the teaching of the present disclosure, add, delete, or amendany components in the radiation delivery device 110 or 400. Suchamendment is also under the protection scope of the present application.Unless otherwise stated, components with the same names in the radiationdelivery device 110 and the radiation delivery device 400 may have thesame or similar functions.

The imaging radiation source 410, the treatment radiation source 430,the MLC 450, and the radiation detector 420 may be mounted on a rotaryring 440. In some embodiments, the radiation delivery device 400 mayinclude a gantry 470 to accommodate a bore 480 and a bed 460. The bed460 may be configured to support the object (e.g., a patient) and/ortransport the object to the gantry 470, where the object may be to beimaged and/or undergo radiotherapy.

The treatment radiation source 430 may be configured to deliver atreatment beam toward a treatment region of the object. For example, theprocess of delivering the treatment beam toward the treatment region ofthe object may refer to a radiotherapy (RT) treatment. The treatmentregion may include a cell mass, a tissue, an organ (e.g., a prostate, alung, a brain, a spine, a liver, a pancreas, a breast, etc.), or acombination thereof. In some embodiments, the treatment region mayinclude a tumor, an organ with a tumor, or a tissue with a tumor. Thetreatment beam may include a particle beam, a photon beam, an ultrasoundbeam (e.g., a high intensity focused ultrasound beam), or the like, or acombination thereof. The particle beam may include a stream of neutrons,protons, electrons, heavy ions, or the like, or a combination thereof.The photon beam may include an X-ray beam, a γ-ray beam, an α-ray beam,a β-ray beam, an ultraviolet beam, a laser beam, or the like, or acombination thereof. The shape of the X-ray beam may be a line, a narrowpencil, a narrow fan, a fan, a cone, a wedge, or the like, or acombination thereof. The energy level of the treatment beam may besuitable for radiotherapy. For example, an X-ray beam delivered by thetreatment radiation source 430 may have an energy of the megavoltage(MV) level. Merely by way of example, the energy of the X-ray beamemitted by the treatment radiation source 430 may be 6 MV.

In some embodiments, the treatment radiation source 430 may be activatedand emit a treatment beam to the treatment region according to apredetermined treatment plan. The predetermined treatment plan mayinclude parameters associated with one or more radiation segments. Theradiation segment may be an arc-shaped segment on the rotationtrajectory of the rotary ring at which treatment radiation source 430delivers the treatment beam to the treatment region. The parametersassociated with the radiation segments may include a desired segmentshape (e.g., a desired shape of the aperture formed by the MLC 450), adesired segment intensity (e.g., a desired segment MU value, a desiredsegment MU rate), a desired segment angle range, and/or a desiredrelative position of the object relative to the rotary ring 440. Forexample, the treatment radiation source 430 may start the delivery ofthe treatment beam to the treatment region when a desired segment anglerange is reached during the rotation of the rotary ring 440 based on thetreatment plan. In some embodiments, the intensity of the treatmentradiation source 430, the position of the bed 460, and/or the shape ofthe leaves in the MLC 450 (which corresponds to the shape of theaperture formed by the MLC 450) may also be adjusted based on thepredetermined treatment plan. During the treatment, the motion of thetreatment region may be tracked, and the real-time location of thetreatment region may be determined by a processing device 140 based onimage data generated by the imaging radiation source 410 and theradiation detector 420. In some embodiments, the treatment radiationsource 430 may include a linear accelerator (LINAC) configured togenerate the treatment beam.

In some embodiments, the radiation delivery device 400 may furtherinclude a treatment beam detector (not shown in the figure) placed onthe rotary ring 440 opposite to the treatment radiation source 430. Thetreatment beam detector may be configured to detect and/or receiveradiation associated with the beams (e.g., X-ray treatment beams)emitted from the treatment radiation source 430 (which may beattenuated). The treatment beam detector may detect and/or receiveradiation associated with the beams emitted from the treatment radiationsource 430 during and/or before a radiotherapy operation performed bythe treatment radiation source 430. For example, during the radiotherapyoperation performed by the treatment radiation source 430, the treatmentbeam detector may detect the radiation associated with the beams emittedfrom the treatment radiation source 430 and monitor the condition (e.g.,the radiation dose) of the radiotherapy. As another example, before theradiotherapy operation, the treatment radiation source 430 may deliver apre-treatment beam, and the treatment beam detector may detect radiationassociated with at least portion of the pre-treatment beam forcalibration (e.g., a calibration of the radiation dose). In someembodiments, the shape of the treatment beam detector may be flat,arc-shaped, circular, or the like, or a combination thereof. Forexample, the treatment beam detector may be a flat panel detectorconfigured to detect radiation emitted by the treatment radiation source430 after attenuation by the object.

The imaging radiation source 410 and the radiation detector 420 (whichare also referred to an imaging assembly collectively) may be configuredto provide image data for generating an image of the treatment region(or an imaging region that overlaps with the treatment region), whichmay be used to determine a real-time location of the treatment region,and/or track the motion of the treatment region during a radiotherapyoperation performed by the treatment radiation source 430. In someembodiments, the location of the treatment region of the object maychange with time due to various motions, for example, cardiac motion(and its effect on other organs), respiratory motion (of the lungsand/or the diaphragm, and its effect on other organs), blood flow andmotion induced by vascular pulsation, muscles contraction andrelaxation, secretory activity of the pancreas, or the like, or acombination thereof. The location of the treatment region may bemonitored based on an image (e.g., a CT image, a cone beam computedtomography (CBCT) image, an MRI image, a PET image, a PET-CT image) ofthe object generated according to the image data acquired by the imagingassembly before, during, and/or after the radiotherapy operation.

In some embodiments, the imaging radiation source 410 may be configuredto emit an imaging beam to the object. The imaging beam may include aparticle beam, a photon beam, or the like, or a combination thereof. Theparticle beam may include a stream of neutrons, protons, electrons,heavy ions, or the like, or a combination thereof. The photon beam mayinclude an X-ray beam, a γ-ray beam, an α-ray beam, a β-ray beam, anultraviolet beam, a laser beam, or the like, or a combination thereof.The shape of the X-ray beam may be a line, a narrow pencil, a narrowfan, a fan, a cone, a wedge, a tetrahedron, or the like, or acombination thereof. For example, the radiation source may be a conebeam computed tomography (CBCT) radiation source and the imaging beammay be a cone beam. In some embodiments, the cone angle of the imagingbeam may be larger than the cone angle of the treatment beam. The coneangle may be defined as an angle formed between two lines connecting anapex and two end points on a diameter of a cross-section of acone-shaped beam. More particularly, when the rotary ring 440 rotates,the space covered by the imaging beam may be larger than the spacecovered by the treatment beam. The energy level of the imaging beam maybe suitable for imaging. In some embodiments, the energy level of theimaging beam may be the same as or different from that of the treatmentbeam generated by the treatment radiation source 430. For example, anX-ray beam delivered by the imaging radiation source 410 may have anenergy of a kilovoltage (kV) level. Merely by way of example, the energyof the X-ray beam may be 90 kV.

Key to the teachings contained herein is the concept of a cone beamX-ray imaging system, and cone beam computed tomography (CBCT). In thevast majority of X-ray imaging systems, X-rays are produced by aBremsstrahlung process in which electrons are incident on an X-raytarget. The electrons lose kinetic energy in the target, and this energyis converted to heat and X-rays. X-rays are emitted in all directions.In reflection targets (such as those used in the vast majority ofdiagnostic X-ray imaging systems), the X-rays emitted in the directionof the target are substantially absorbed by the target. The X-rays thatleave the target are emitted over a wide solid angle. These rays usuallyleave the X-ray tube through an exit window that is substantiallytransparent to x-rays. When the exit window is circular, the shape ofthe beam is a true cone. However, most systems (e.g., in planarradiography applications) collimate the beam to a rectangular crosssection. Nevertheless, such a beam is also termed a cone beam. In singleslice CT systems, the cone beam is much more narrowly collimated alongthe long axis of the patient (direction that patient couch travels) thanlateral axis (usually along the plane of rotation of the imagingsystem). Such a beam is typically referred to as a fan beam, rather thana cone beam, even though the beam may, before collimation, have assumedthe form of a cone. In multislice CT (and helical scan implementationsof multislice CT), the detector typically has larger axial extent thanin the fan beam CTs. However, it is not typical to refer to the beam ofa multislice CT as a cone beam, since it is much more substantiallycollimated in the axial direction as compared to the lateral direction.

Linear accelerator X-ray sources (e.g., the treatment radiation source430 and the imaging radiation source 410) almost universally rely onBremsstrahlung from transmission targets to generate photon beams. Likereflection sources, transmission targets also generate X-rays thattravel in all directions. However, the target is itself substantiallytransparent to the emerging X-rays. The higher the energy of theincident electrons, the more concentrated is the flux of photons in theforward (transmission) direction (directions more closely aligned withthat of the original electron beam). The emerging photon beams arealmost always collimated by a conical primary collimator, formingsubstantially a cone beam. However, this cone beam may be furthercollimated. In most systems, collimation is achieved by rectangular jawsand/or a 2D multileaf collimator. In the present disclosure, suchfurther collimated beams are also termed cone beams. In contrast, aminority of radiation therapy systems, such as that described in U.S.Pat. No. 5,548,627 (which describes the basis of the Tomotherapy line ofradiation therapy systems), are designed to produce a beam “only withinthe gantry plane.” The gantry plane in such systems is substantiallynarrower than the lateral extent of the patient and the treatment field.This narrow collimation along the long axis of the patient, by analogywith the fan beam CT and multislice CT cases, means that such a beam isnot considered a cone beam by people having ordinary skills in the artof x-ray imaging and therapy systems. In fan beam CT, multislice CT, andtomotherapy, the patient support is almost always translated along thelong axis of the patient in order to image and/or treat all volumes ofinterest. In cone beam CT, and therapy with 2D (collimated) cone beams,the patient support is almost never moved to accomplish imaging and/ortreatment of volumes of interest.

In view of the above, the term “cone angle” as applied to a collimatedcone beam, is taken to be the angle subtended at the source of thecollimated beam, by the edges of the collimated field, in the particulardirection along with the field is collimated. Understanding of theteachings contained herein require the disambiguation of the concept ofa “CT detector” (e.g., the radiation detector 420). For CBCT, flat paneldetectors are normally used. These detectors almost always have arelatively large area (e.g. 8 in×8 in, 16×16 in, 40 cm×30 cm), and lowaspect ratio (ratios of length to width such as 1:1 and 4:3). Incontrast, CT detectors may not be flat, and have much higher aspectratios, where the arc length of the detector in the plane of rotation(lateral extent, or fan angle) greatly exceeds the axial dimension (andsubjected axial angle from the source) of the detector. In most cases,CT detectors are arranged along an isocentric arc at the same radius asthe source. In most cases, CT detector assemblies include a collimatorthat collimates the detector elements to the source. In effect, eachaxial detector row is collimated to a fan beam.

The radiation detector 420 may be configured to detect or receiveradiation associated with at least a portion of the imaging beam emittedfrom the imaging radiation source 410 to generate imaging data (e.g.,projection data). The imaging data may be transmitted to the processingdevice 140 for further processing. The processing device 140 mayreconstruct an image of the object or a portion thereof based on theimaging data. The location of the treatment region of the object may bedetermined based on the image.

In some embodiments, the radiation detector 420 may include one or moredetector units. A detector unit may include a scintillator layer (e.g.,a cesium iodide scintillator layer, a gadolinium oxysulfide scintillatorlayer), a gas detector, etc. In some embodiments, the detector units maybe arranged in a single row, two rows, or any other number of rows.Merely by way of example, the radiation detector 420 may be a CTdetector configured to detect X-rays (e.g., radiation emitted by theimaging radiation source 410 after attenuation by the object). The shapeof the radiation detector 420 may be flat, arc-shaped, circular, or thelike, or a combination thereof. For example, the radiation detector 420may be a flat panel detector. In some embodiments, a dual layerdetector, or photon counting detector, may be employed to obtain energyinformation from the impinging X-ray beam.

The gantry 470 may be configured to support one or more components ofthe radiation delivery device 110 (e.g., the treatment radiation source430, the treatment beam detector, the imaging radiation source 410, theradiation detector 420). In some embodiments, the gantry 470 may includea movement restriction component configured to limit the movement (e.g.,the movement along the Z-direction) of the rotary ring 440. The movementrestriction component may also protect one or more components of theradiation delivery device 400 from swinging out from the radiationdelivery device 400 during the movement of the rotary ring 440. Merelyby way of example, the movement restriction component may be a housingoutside the rotary ring 440 (and/or the components thereof). Themovement restriction component may be attached to the inner surface ofthe gantry 470.

In some embodiments, the radiation delivery device 400 may furtherinclude a cooling device (not shown in the figure). The cooling devicemay be configured to produce, transfer, deliver, channel, or circulate acooling medium to the radiation delivery device 400 to absorb heatproduced by the radiation delivery device 400 (e.g., the radiationdetector 420) during an imaging procedure and/or radiotherapy operation.The bed 460 may be configured to support and/or transport the object(e.g., a patient) to be imaged and/or undergo radiotherapy.

FIG. 5 is a schematic diagram illustrating an exemplary slip ringaccording to some embodiments of the present disclosure. As shown inFIG. 5, the slip ring 500 may include a stationary portion 510, aconnector 520, and a rotary portion 540. In some embodiments, thestationary portion 510 may be fixed, and the rotary portion 540 mayrotate around its center axis (i.e., the dotted line). The rotaryportion 540 and the stationary portion 510 may be connected to eachother via the connector 520. The stationary portion 510 may beelectrically connected to a power supply (e.g., a three-phase electricmains). The stationary portion 510 may extract electricity from thepower supply and transmit the electricity via cables inside thestationary portion 510 to three conducting ports 550 (which maycorrespond to a live cable, a neutral cable, and a ground cable,respectively). The three conducting ports 550 may touch and beelectrically connected to three conducting bars 530 mounted on thesurface of the rotary portion 540, respectively. The conducting bars maybe continuously connected to the corresponding conducting barsregardless of whether the rotary portion 540 is rotating or at rest. Insome embodiments, the rotary portion 540 may be connected to a rotaryring (e.g., the rotary ring 114, the rotary ring 440). As such, the slipring 500 may enable the rotary ring 114 to rotate continuously aroundthe object and supply power to the components mounted on the rotary ring114 (e.g., the first radiation source 113, the second radiation source111 and/or the radiation detector 112). The slip ring 500 may alsotransmit one or more of the following data: control data to and from thelinear accelerator, control and image data to and from the imagingdetectors paired within the first radiation source and second radiationsource, control data (such as exposure, beam energy and x-ray pulsetiming) to and from the second radiation source.

In some embodiments, the slip ring may be replaced by any kind ofrotatable component, such as a gear, a reel, a rotation shaft, etc. Forexample, a rotation of the rotary ring 114 is driven via at least one ofa slip ring, a gear, a reel, or a rotation shaft. In a case that thekind of rotatable component cannot supply power to the rotary ring 630,the power of the rotary ring 630 and/or components thereof (e.g., theimaging source 410, the radiation detector 420, and/or the treatmentsource 430) may be supplied by a battery or supercapacitor placed insidethe rotary ring 630. As another example, rotary ring 630 and/orcomponents thereof may be charged by a wireless charging device, or thelike.

FIG. 6 is a schematic diagram illustrating an exemplary connection of arotary ring and a slip ring according to some embodiments of the presentdisclosure. As shown in FIG. 6, radiation delivery device 600 mayinclude a gantry 610, a connector 620, and a stationary portion 640 of aslip ring, and a rotary ring 630. The stationary portion 640 may befixedly connected to the gantry 610 and may remain at rest when therotary portion (or the rotary ring 630) rotates. The rotary ring 630 maybe mounted on a rotary portion (not shown in the figure). In someembodiments, the connector 620 may each include three conducting ports(similar to the conducting ports 550). The rotary portion (or the rotaryring 630) may include three conducting bars around its circumference.Conducting ports of the connector 620 may touch and be electricallyconnected to the conducting bars at respective locations. The connector620 can both hold and supply power to the rotary ring 630.

FIG. 7A and FIG. 7B are schematic diagrams illustrating differentconfigurations of an exemplary radiation delivery device according tosome embodiments of the present disclosure. In some embodiments, FIG. 7Aand FIG. 7B may correspond to the same radiation delivery device 700before and after a rotation, respectively. In some embodiments, theradiation delivery device 700 may be an exemplary embodiment of theradiation delivery device 110 but shall not be considered as the onlypossible configuration of the radiation delivery device 110. Peoplehaving ordinary skill in the art may, under the teaching of the presentdisclosure, add, delete, or amend any components in the radiationdelivery device 110 or 700. Such amendment is also under the protectionscope of the present application. Unless otherwise stated, componentswith same names in the radiation delivery device 110 and the radiationdelivery device 700 may have similar functions.

As shown in FIG. 7A, the radiation delivery device 700 may include atreatment radiation source 730 (also referred to as a first radiationsource), an imaging radiation source 710 (also referred to as a secondradiation source), a radiation detector 720, a rotary ring 740, an MLC750 and a gantry 760. An object 770 (e.g., a patient) may lie on a bed(not shown in the figure). The object 770 may include a tumor region 780and be scanned and/or undergo radiotherapy. In some embodiments, thetreatment radiation source 730 may emit a treatment beam toward atreatment region of an object 770. The MLC 750 may include a pluralityof leaves that form an aperture. The aperture may modify the shape ofthe treatment beam. The MLC 750 may be moved during the rotation of therotary ring 740 according to a treatment plan.

The imaging radiation source 710 may emit an imaging beam toward animaging region of the object 770. The radiation detector 720 may receivean attenuated imaging beam that transmits through the imaging region,and generate image data associated with the imaging region. In order toobtain an image data of the treatment region of the object 770, theimaging region may include or overlap with the treatment region. As usedherein, a treatment region (or an imaging region) may be defined as aregion that the treatment beam impinges upon the object 770. Ideally,the treatment region associated with the radiotherapy may coincide withthe tumor region 780 of the object 770.

In some embodiments, the radiation delivery device 700 may operate basedon a treatment plan. The treatment plan may include a plurality ofparameters associated with one or more radiation segments. The radiationsegment may be an arc-shaped segment on the rotation trajectory of therotary ring at which treatment radiation source 730 delivers thetreatment beam to the treatment region. The parameters associated withthe one or more radiation segments may include a desired segment shape,a desired segment intensity (e.g., a desired segment MU value, a desiredsegment MU rate), a desired segment angle range, and/or a desiredrelative position of the object relative to the rotary ring 740. In someembodiments, when the rotary ring 740 rotates, the imaging radiationsource 710 may emit an imaging beam during the whole or most of the 360degrees (also referred to as a full rotation) of the rotation of therotary ring 740, and the radiation detector 720 may detect radiationassociated with the imaging beam. However, the treatment radiationsource 730 may operate only at the desired segment angle ranges (e.g.,from 0 degrees to 20 degrees, from 65 degrees to 90 degrees) based onthe treatment plan. When the treatment radiation source 730 reaches aradiation segment, the MLC 750 may also change the shape of the apertureit forms based on desired segment shape of the treatment plan.

In some embodiments, FIG. 7A illustrates a configuration of a radiationdelivery device 700 before the rotation of the rotary ring 740. FIG. 7Billustrates a configuration of the same radiation delivery device 700after a 90 degrees rotation of the rotary ring 740. It may be noted fromFIG. 7A and FIG. 7B that the angular offset between the treatmentradiation source 730 and the imaging radiation source 710 (and/or theradiation detector 720) in the plane of rotation of the rotary ring 740may remain unchanged during the rotation of the rotary ring 740. It maybe understood that the rotary ring 740 may continue to rotate, and whenthe rotary ring 740 rotates for 360 degrees (i.e., a rotary ring rotatesa full rotation), the components of the radiation delivery device 700may return to their initial positions similar to their respectivepositions illustrated in FIG. 7A.

In some embodiments, a full rotation in the present disclosure maygenerally refer to a rotation of 360 degrees (of the rotary ring).However, the imaging or the treatment process disclosed in the presentapplication may only last for a portion of the 360 degrees. Hence, thefull rotation may also refer to a rotation of certain degrees less thanor equal to 360 degrees (e.g., 270 degrees, 300 degrees) that theimaging or the treatment process disclosed in the present application isfinished or the detected treatment result or image data is sufficientfor further processing.

FIG. 8 is a schematic diagram illustrating an exemplary multi-leafcollimator (MLC) according to some embodiments of the presentdisclosure. The multi-leaf collimator (MLC) 800 may include a pluralityof leaves 810, a rail box 820, a plurality of motors 830, and a housing840. Each of the motors 830 may control the movement (e.g., a linearmovement) of a corresponding leave 810. The plurality of motors 830 maybe controlled by a processing device (e.g., the processing device 140)such that they may move the plurality of leaves in a controlled way(e.g., based on a treatment plan) to form a desired shape of theaperture.

FIG. 9 is a schematic diagram illustrating a shape of an exemplaryaperture formed by an MLC and corresponding treatment region. In someembodiments, the MLC 900 may be placed between a treatment radiationsource (e.g., the first radiation source 113, the treatment radiationsource 430, the treatment radiation source 730) and a bore (e.g., bore117). The MLC 900 may modify the shape of the beam emitted from theradiation source to a shape similar to the aperture 930 formed by theleaves 920 of the MLC. In some embodiments, the processing device 140may obtain a treatment plan. The treatment plan may include a desiredsegment shape of a radiation segment. The desired segment shape maycorrespond to the shape of desired treatment region 940. The leaves 920of the MLC may be moved based on the treatment plan such that theaperture 930 formed by the leaves 920 may modify the shape of the beamemitted from the radiation source. The modified beam may be deliveredtoward and match (or approximately match) the desired treatment region940.

FIG. 10 is a block diagram illustrating an exemplary processing deviceaccording to some embodiments of the present disclosure. The processingdevice 140 may include an acquisition module 1010, a control module1020, a processing module 1030, and a storage module 1040. At least aportion of the processing device 140 may be implemented on a computingdevice as illustrated in FIG. 2 or a mobile device as illustrated inFIG. 3.

The acquisition module 1010 may acquire imaging data. In someembodiments, the acquisition module 1010 may acquire the imaging data(e.g., CT imaging data) from the radiation delivery device 110, theterminal 130, the storage device 150, and/or an external data source(not shown). In some embodiments, the imaging data may include raw data(e.g., projection data). For example, the imaging data (e.g., projectiondata) may be generated based on detected imaging beams at least some ofwhich have passed through an object being imaged and treated in theradiation delivery device 110. In some embodiments, the acquisitionmodule 1010 may acquire one or more instructions for processing theimaging data. The instructions may be executed by the processor(s) ofthe processing device 140 to perform exemplary methods described in thisdisclosure. In some embodiments, the acquired imaging data may betransmitted to the storage module 1040 to be stored.

In some embodiments, the acquisition module 1010 may acquire a treatmentplan for an object. The treatment plan may include parameters associatedwith at least one radiation segments. The radiation segment may be anarc-shaped segment on the rotation trajectory of the rotary ring atwhich the treatment radiation source delivers the treatment beam to thetreatment region. The acquisition module 1010 may acquire the treatmentplan from one or more components of the radiation system 100 (e.g., thestorage device 150, the terminal 130), or from an external source (e.g.,an electronic medical record, a medical database) via the network 120.

The control module 1020 may control operations of the acquisition module1010, the storage module 1040, the processing module 1030 (e.g., bygenerating one or more control parameters), the radiation deliverydevice 110, or the like, or a combination thereof. For example, thecontrol module 1020 may cause the acquisition module 1010 to acquireimaging data, the timing of the acquisition of the imaging data, etc. Asanother example, the control module 1020 may cause the processing module1030 to process imaging data acquired by the acquisition module 1010. Insome embodiments, the control module 1020 may control the operation ofthe radiation delivery device 110. For example, the control module 1020may cause the radiation delivery device 110 (e.g., the treatmentassembly) to start, pause, stop, and/or resume the delivery of theimaging beam and/or the treatment beam to the object. As anotherexample, the control module 1020 may cause the radiation delivery device110 to adjust the radiation dose of the imaging beam or treatment beamto the object.

In some embodiments, the control module 1020 may receive a real-timeinstruction from an operator or retrieve a predetermined instructionprovided by a user (e.g., a doctor) to control one or more operations ofthe radiation delivery device 110, the acquisition module 1010, and/orthe processing module 1030. For example, the control module 1020 mayadjust the acquisition module 1010 and/or the processing module 1030 togenerate one or more images of an object according to the real-timeinstruction and/or the predetermined instruction. As another example,the control module 1020 may cause the radiation delivery device 110 toadjust the treatment beam delivered to the object according to thereal-time instruction and/or the predetermined instruction. As a furtherexample, the control module 1020 may gate and/or adjust the delivery ofthe treatment beam of the treatment assembly based on real-timemonitoring of the location of the treatment region of the objectaccording to the generated image(s). As still a further example, thecontrol module 1020 may cause the position of the bed 115 and/or thetreatment assembly (e.g., the first radiation source 113) to be adjustedaccording to the generated image(s), so that the treatment beam maytarget the treatment region of the object. In some embodiments, thecontrol module 1020 may communicate with one or more other modules ofthe processing device 140 for exchanging information and/or data.

The processing module 1030 may process information provided by variousmodules of the processing device 140. The processing module 1030 mayprocess imaging data acquired by the acquisition module 1010, imagingdata retrieved from the storage module 1040 and/or the storage device150, etc. In some embodiments, the processing module 1030 mayreconstruct one or more images based on the imaging data according to areconstruction technique. The reconstruction technique may include aniterative reconstruction algorithm (e.g., a statistical reconstructionalgorithm), a Fourier slice theorem algorithm, a filtered backprojection (FBP) algorithm, a fan-beam reconstruction algorithm, ananalytic reconstruction algorithm, or the like, or a combinationthereof. The reconstruction technique may be applied over a limitedangular range to perform tomosynthesis imaging. In some embodiments, theprocessing module 1030 may perform pre-processing on the imaging databefore the reconstruction. The pre-processing may include, for example,imaging data normalization, imaging data smoothing, imaging datasuppressing, imaging data encoding (or decoding), denoising, etc.

In some embodiments, based on one or more reconstructed images of anobject including a treatment region, the processing module 1030 maydetermine a change of location or shape of the treatment region. In someembodiments, the processing module 1030 may determine, based on theimages and the analysis thereof, whether any change or adjustment isneeded with respect to the treatment plan, and/or determine the neededadjustment. According to the determined adjustment, the control module1020 may cause the adjustment to be implemented. For instance, thecontrol module 1020 may cause the radiation delivery device 110 todeliver an adjusted treatment beam or adjust a position of the object.For example, the processing module 1030 may transmit the motioninformation of the treatment region to the control module 1020. Thecontrol module 1020 may accordingly control the radiation deliverydevice 110 to adjust the delivery of the treatment beam by, for example,pausing the delivery and/or changing the position of the source of thetreatment beam. As another example, the control module 1020 mayaccordingly control the radiation delivery device 110 to adjust theposition of the object with respect to the treatment beam.

In some embodiments, the delivery of a treatment plan may be monitoredand/or adjusted real time. For instance, based on the imaging data theimaging scan components and/or the acquisition module 1010 acquires(e.g., real time), the processing module 1030 may automatically generateand/or analyze images to monitor the location of the treatment region ofthe object, and/or assess the change of the location of the treatmentregion, on the basis of which the processing module 1030 may determinehow to proceed further with the treatment plan (e.g., to continue theradiotherapy as planned, to continue the radiotherapy with a revisedplan, or to terminate the radiotherapy, etc.). The processing module1030 may determine the location of the treatment region based on thegenerated image(s). In some embodiments, the monitoring, assessment,and/or adjustment may be performed semi-automatically with the input ofa user. For instance, based on the imaging data the imaging scancomponents and/or the acquisition module 1010 acquires (e.g., realtime), the processing module 1030 may generate one or more images andsend them to be presented on a terminal 130 (e.g., a display) so thatthe user may analyze the images and provide an instruction as to how toproceed further with the treatment plan (e.g., to continue theradiotherapy as planned, to continue the radiotherapy with a revisedplan, or to terminate the radiotherapy, etc.). The processing module1030 may determine accordingly if any adjustment in the treatment planis needed. If the change of location or shape of the target region or iswithin a threshold, the processing module 1030 may determine theadjustment automatically and send it to, e.g., the control module 1020,to be implemented. In some embodiments, a notification may be generatedwhen the processing module 1030 makes such a determination. If thechange of location or shape of the target region is not within athreshold, the processing module 1030 may generate a notification to,e.g., the user (e.g., the doctor), to seek instructions from the user asto how to proceed further.

The storage module 1040 may store imaging data, control parameters,processed imaging data, treatment plan, adjusted treatment plan, or thelike, or a combination thereof. In some embodiments, the storage module1040 may store one or more programs and/or instructions that may beexecuted by the processor(s) of the processing device 140 to performexemplary methods described in this disclosure. For example, the storagemodule 1040 may store program(s) and/or instruction(s) that can beexecuted by the processor(s) of the processing device 140 to acquireimaging data of an object, reconstruct one or more images based on theimaging data, determine an ROI in the image(s), detect a change oflocation or shape of a treatment region of the object based on theimage(s), revise the delivery of the treatment beam to the treatmentregion, and/or adjust the position of the object relative to thetreatment beam based on the detected change of location or shape of thetreatment region.

In some embodiments, one or more modules illustrated in FIG. 10 may beimplemented in at least part of the radiation system 100 as illustratedin FIG. 1. For example, the acquisition module 1010, the control module1020, the processing module 1030, and/or the storage module 1040 may beimplemented via the processing device 140 and/or the terminal 130.

FIG. 11 is a schematic diagram illustrating an exemplary process of CTscans and RT treatments in different rotations according to someembodiments of the present disclosure. In some embodiments, CT scansand/or RT treatment in each row of FIG.11 may correspond to a rotation(or a rotation of 360 degrees) of a rotary ring (e.g., the rotary ring114, the rotary ring 440, the rotary ring 630, the rotary ring 740). Forexample, the 2^(nd) CT scan 1125 and the 2^(nd) RT treatment 1120 maycorrespond to a second rotation. The CT scan may be performed by animaging assembly (e.g., the second radiation source 111 and theradiation detector 112, the imaging radiation source 410 and theradiation detector 420, the imaging radiation source 710 and theradiation detector 720). The RT treatment may be performed by atreatment radiation source (e.g., the first radiation source 113, thetreatment radiation source 430, the treatment radiation source 730). Asshown in FIG. 11, an RT treatment in a present rotation may be relatedto a CT scan result and an RT treatment in a preceding rotation. Forexample, the 5^(th) RT treatment 1150 may be related to a 3^(rd) CT scan1145 and a 4^(th) RT treatment 1140. More particularly, each rotation ofthe rotary ring may be associated with a treatment plan. The treatmentplan may include a plurality of parameters associated with one or moreradiation segments. The radiation segment may be an arc-shaped segmenton the rotation trajectory of the rotary ring at which the treatmentradiation source delivers the treatment beam to the treatment region.The parameters associated with the one or more radiation segments mayinclude a desired segment shape, a desired segment intensity (e.g., adesired segment MU value, a desired segment MU rate), a desired segmentangle range, and/or a desired relative position of the object relativeto the rotary ring.

In some embodiments, the treatment plan or parameters thereof in apreceding rotation may be adjusted based on a CT scan result (e.g., CTimage data) in the preceding rotation. The RT treatment in a presentrotation may be determined by the adjusted treatment plan. In someembodiments, the processing module 1030 may cause the rotary ring torotate a first full rotation and a second full rotation, the second fullrotation being after the first full rotation. The processing module 1030may then adjust, based on radiation detected by the radiation detectorin the first full rotation, parameters associated with the radiationsegments at which the first radiation source emits a first cone beam inthe second full rotation. Further, the processing module 1030 maycontrol an emission of the first cone beam based on the adjustedparameters associated with the radiation segments. Similarly, theprocessing module 1030 may adjust, based on radiation detected by theradiation detector in the second full rotation, parameters associatedwith radiation segments at which the first radiation source emits afirst cone beam in the third full rotation and control an emission ofthe first cone beam based on the adjusted parameters. The similarprocesses of adjusting parameters associated with the radiation segmentsand controlling the emission of the first cone beam based on adjustedparameters may be performed repeatedly in subsequent rotations.

In some embodiments, the processing module 1030 may adjust, based onradiation detected by the radiation detector in a present rotation,parameters associated with the radiation segments that follow theradiation detection by the radiation detector in the present rotation.The processing module 1030 may control the RT treatment (or the emissionof the first cone beam) at the radiation segments that follow theradiation detection by the radiation detector based on the adjustedparameters associated with the radiation segments in the presentrotation.

FIG. 12 is a flowchart illustrating an exemplary process for controllinga rotation of the rotary ring based on respiration information of anobject. In some embodiments, one or more operations of process 1200 maybe implemented in the radiation system 100 illustrated in FIG. 1. Forexample, the process 1200 may be stored in the storage device 150 and/orthe storage 220 in the form of instructions (e.g., an application), andinvoked and/or executed by the processing device 140 (e.g., theprocessor 210 of the computing device 200 as illustrated in FIG. 2, theCPU 340 of the mobile device 300 as illustrated in FIG. 3, one or moremodules of the processing device 140 as illustrated in FIG. 10, or thelike). As another example, at least a portion of the process 1200 may beimplemented on the radiation delivery device 110. The operations of theillustrated process presented below are intended to be illustrative. Insome embodiments, the process 1200 may be accomplished with one or moreadditional operations not described, and/or without one or more of theoperations discussed. Additionally, the order in which the operations ofthe process 1200 as illustrated in FIG. 12 and described below is notintended to be limiting.

In 1210, the processing module 1030 may obtain respiration informationof the object. The respiration information of the object may include anaverage respiration period, a minimum respiration period, a maximumrespiration period of the object. In some embodiments, the respirationperiod may be defined as a period that the object inhales and exhales.The respiration information of the object may also include the averageinhale period and average exhale period.

In some embodiments, the respiration information may be obtained by arespiration information acquisition device. For example, the respirationinformation acquisition device may be a camera. The camera may beconfigured to monitor the mouth of the object and determine therespiration information based on the shape and size of the mouth. Asanother example, the respiration information acquisition device mayinclude a gas detector (e.g., an air mask). The gas detector may beplaced on the mouth and/or nose of a patient and act as an airexchanging channel. The respiration information may be determined basedon the air flowing in/out of the air exchange channel.

In 1220, the processing module 1030 may determine a rotation parameterof the rotary ring based on the respiration information of the user.Merely by way of example, the respiratory motion of the lungs and/or thediaphragm, and its effect on other organs may influence the quality ofCT scan or the radiotherapy treatment disclosed elsewhere in the presentapplication. The rotation speed (i.e., a rotation parameter) of therotary ring may be controlled to reduce the influence of the respiratorymotion. In some embodiments, the rotation speed (or the rotationparameter) of the rotary ring may be controlled to be not more than halfof the average respiration period. For example, the rotation speed (orthe rotation parameter) of the rotary ring may be controlled to 1rotation per second if the average respiration period is 3 seconds. Insome embodiments, the period that the rotary ring rotates a fullrotation may be less than 30 seconds. In some embodiments, the periodthat the rotary ring rotates a full rotation may be a fixed value, e.g.,1 second, 2 seconds, 5 seconds, 10 seconds, 30 seconds, etc. As anotherexample, the rotation speed of the rotary ring may be changeddynamically based on the average respiration period or other respirationinformation.

In 1230, the processing module 1030 may control a rotation of the rotaryring based on the rotation parameter. For example, the processing module1030 may send an instruction to the motor of the rotary ring to increaseor decrease the rotation speed of the rotary ring.

FIG. 13 is a flowchart illustrating an exemplary process for controllingemissions of beams from a first radiation source and a second radiationsource. In some embodiments, one or more operations of process 1300 maybe implemented in the radiation system 100 illustrated in FIG. 1. Forexample, the process 1300 may be stored in the storage device 150 and/orthe storage 220 in the form of instructions (e.g., an application), andinvoked and/or executed by the processing device 140 (e.g., theprocessor 210 of the computing device 200 as illustrated in FIG. 2, theCPU 340 of the mobile device 300 as illustrated in FIG. 3, one or moremodules of the processing device 140 as illustrated in FIG. 10, or thelike). As another example, at least a portion of the process 1300 may beimplemented on the radiation delivery device 110. The operations of theillustrated process presented below are intended to be illustrative. Insome embodiments, the process 1300 may be accomplished with one or moreadditional operations not described, and/or without one or more of theoperations discussed. Additionally, the order in which the operations ofthe process 1300 as illustrated in FIG. 13 and described below is notintended to be limiting.

In 1310, the acquisition module 1010 may obtain a treatment plan for anobject. The treatment plan may include parameters for controlling thedelivered radiation to be delivered to a treatment region (e.g., a tumorregion) and sparing the surrounding healthy tissue surrounding thetreatment region from the radiation damage. The treatment plan may bedetermined based on a set of one or more optimization goals and/or oneor more constraints of a radiation delivery device (e.g., the radiationdelivery device 110). The treatment plan may include parametersassociated with at least one radiation segment. The radiation segmentmay be an arc-shaped segment on the rotation trajectory of the rotaryring at which a treatment radiation source (e.g., the first radiationsource 113, the treatment radiation source 430, the treatment radiationsource 730) delivers the treatment beam to the treatment region. Theparameters associated with the radiation segments may include a desiredsegment shape (e.g., a desired shape of the aperture formed by an MLC(e.g., the MLC 450, the MLC 750, the MLC 900)), a desired segmentintensity (e.g., a desired segment MU value, a desired segment MU rate),a desired segment angle range, and/or a desired relative position of theobject relative to the rotary ring. Details regarding the generation ofthe treatment plan may be found in PCT application No.PCT/CN2018/085279, entitled “SYSTEMS AND METHODS FOR GENERATINGRADIATION TREATMENT PLAN” filed on May 2, 2018 (Attorney Docket No.20618-0341WO00), the disclosure of which is expressly incorporatedherein to its entirety.

In some embodiments, the acquisition module 1010 may obtain thetreatment plan from one or more components of the radiation system 100,such as a storage device (e.g., the storage device 150), a terminal(e.g., the terminal 130), or the like. Alternatively, or additionally,the acquisition module 1010 may obtain the treatment plan from anexternal source via the network 120. For example, the acquisition module1010 may obtain the treatment plan from an electronic medical record, amedical database, etc.

In 1320, the control module 1020 may cause a rotary ring to rotatearound the object. As described elsewhere in the present disclosure, atreatment radiation source (e.g., the first radiation source 113, thetreatment radiation source 430, the treatment radiation source 730), animaging radiation source (e.g., the second radiation source 111, theimaging radiation source 410, the imaging radiation source 710) and aradiation detector (e.g., the radiation detector 112, the radiationdetector 420, the radiation detector 720) may be mounted on the rotaryring (e.g., the rotary ring 114, the rotary ring 440, the rotary ring630, the rotary ring 740), and the rotary ring may rotate around theobject. The angular offset between the treatment radiation source andthe imaging radiation source in the plane of rotation of the rotary ringmay remain unchanged during the rotation of the rotary ring.

It may be desirable to monitor a location or shape of the treatmentregion by imaging the treatment region (or the object), so that theradiotherapy may be guided based on the location of the treatmentregion. The radiotherapy (or a portion of the radiotherapy procedure)may be performed simultaneously with the imaging operation (e.g., a 3-Dimaging) during the rotation of the rotary ring. In some embodiments,the 3-D imaging may include generating a 3-D image based on a receivedradiation associated with either of or both the first cone beam and thesecond beam. Merely by way of example, the first cone beam and thesecond beam may be emitted in a same full rotation or a same fraction ofa full rotation. In some embodiments, the change of location or shape(e.g., the respiratory motion, the cardiac motion) of the treatmentregion of the object may be determined so that the control module 1020may control the rotary ring as well as the treatment radiation sourceand the imaging assembly (including the imaging radiation source and theradiation detector) to rotate at a relatively high speed to ensure thatimage(s) generated by the imaging assembly have relatively high quality(e.g., relatively high clarity, relatively low level of artifact).

In 1330, the control module 1020 may move the plurality of leaves in anMLC based on the treatment plan. The MLC (e.g., the MLC 450, the MLC750, the MLC 900) may modify the shape of the beam emitted from thefirst radiation source 113. The treatment plan may include a desiredsegment shape of a radiation segment. The desired segment shape maycorrespond to a shape of desired treatment region (e.g., the treatmentregion 940). The leaves of the MLC may be moved based on the treatmentplan such that an aperture formed by the leaves may modify the shape ofthe beam emitted from the radiation source. The modified beam may bedelivered toward and match (or approximately match) the desiredtreatment region.

In 1340, the control module 1020 may control a first radiation source toemit a first beam toward a first region of the object based on thetreatment plan. The first radiation source may emit the first beamtoward the treatment region of the object when the rotary ring (or thefirst radiation source) is rotating. In some embodiments, the firstradiation source is a treatment radiation source, and the first regionis a treatment region (e.g., a tumor). Alternatively, the firstradiation source is an imaging radiation source, and the first region isan imaging region.

In some embodiments, the first radiation source may emit a plurality offirst beams to the first region of the object at a plurality ofradiation segments. The beam shapes and beam intensities in differentradiation segments may be different. In some embodiments, the leaves ofthe MLC may be adjusted to provide beam shapes corresponding to theplurality of radiation segments. In some embodiments, the MLC may beadjusted during an interval between two radiation segments.

Merely by way of example, there are two radiation segments, such as afirst segment and a second segment. Before the emission of the radiationbeams, the first radiation source may be rotated to a first radiationposition. The first radiation position may correspond to the radiationsegment angle of a first radiation segment. The MLC may be adjusted to afirst configuration that forms an aperture corresponding to the shape ofthe first radiation segment. Then the control module 1020 may controlthe first radiation source to emit a beam with a first beam intensityduring the rotation in the first radiation segment. When the firstradiation source is about to be out of the radiation angle of the firstradiation segment, the control module 1020 may control the firstradiation source to stop the emission of the beam. The control module1020 may adjust the MLC to a second configuration that forms an aperturecorresponding to the shape of a second radiation segment. When the firstradiation source 113 rotates to the second radiation segment, the MLCmay move its leaves to the second configuration, and the control module1020 may control the first radiation source 113 to emit a beam with asecond beam intensity during the rotation in the second radiationsegment.

In 1350, the control module 1020 may control a second radiation sourceto emit a second beam toward a second region of the object based on thetreatment plan. In some embodiments, the second radiation source mayemit the second beam toward the second region of the object when therotary ring (or the second radiation source) is rotating at a relativelyhigh speed.

In some embodiments, the first radiation source and the second radiationsource may perform the same functions. For example, the first radiationsource and the second radiation source may both be configured to delivertreatment beams to the treatment region, or both configured to generateimage data of the object (including the treatment region). In someembodiments, the first radiation source may be configured to deliverradiation to the treatment region, while the second radiation source maybe configured to generate image data of the object (including thetreatment region).

In 1360, the processing module 1030 may generate a CT image based on theimage data acquired by a radiation detector (e.g., the radiationdetector 112) according to the radiation associated with the first beamand/or the second beam being detected by the radiation detector. Thefirst beam and/or the second beam may be emitted in a same full rotationor in a same fraction of a full rotation. The CT image may include atwo-dimensional (2-D) image, a three-dimensional (3-D) image, or thelike. In some embodiments, the image may include information related toone or more imaging regions of the object (e.g., a tumor, OAR, otherhealthy organs or tissue).

In some embodiments, the imaging assembly may scan the object to acquireimage data continuously or discontinuously. The image data may be usedto reconstruct or generate one or more images of the object. In someembodiments, the imaging assembly may scan the object at a certaininterval (e.g., once every 5 degrees of a rotation, once every 10degrees of a rotation, etc.). In some embodiments, to generate theimage(s) in multiple layers, a bed supporting the object (e.g., the bed115, the bed 460) may be moved, for example, along the Z-axis directionillustrated in FIG. 1. In some embodiments, when the bed is moved, thecontrol module 1020 may cause the treatment radiation source to stop orpause the emission of the radiation beams. In some embodiments, thetreatment plan may take the movement of the bed into consideration, andthe treatment radiation source may keep emitting the radiation beamswhen the bed is moved.

In some embodiments, the processing module 1030 may reconstruct one ormore the image(s) based on the image data acquired by the imagingassembly according to a reconstruction algorithm. The reconstructionalgorithm may include an iterative reconstruction algorithm (e.g., astatistical reconstruction algorithm), a Fourier slice theoremalgorithm, a filtered back projection (FBP) algorithm, a fan-beamreconstruction algorithm, an analytic reconstruction algorithm, or thelike, or a combination thereof.

In 1370, the control module 1020 (and/or the processing module 1030) mayadjust at least part of the treatment plan based on the CT image data.In some embodiments, the processing module 1030 may compare thegenerated CT image data with treatment planning image data. Thetreatment planning image data may refer to image data that are used togenerate or adjust the treatment plan. The processing module 1030 maydetermine whether the treatment plan needs to be adjusted based on aresult of the comparison. In response to a result of the determinationthat the treatment plan needs to be adjusted, the control module 1020may adjust at least part of the treatment plan, for example, at leastone parameters associated with the treatment plan. More descriptionsregarding the adjustment of the treatment plan may be found elsewhere inthe present disclosure (e.g., FIG. 14 and the relevant descriptionsthereof). In some embodiments, the control module 1020 may adjust theposition of the object based on a result of the comparison but notadjust the treatment plan. Alternatively, the control module 1020 mayadjust both the treatment plan and the position of the object.

FIG. 14 is a flowchart illustrating an exemplary process for adjustingthe treatment plan based on the detected radiation associated with thefirst radiation source and/or the second radiation source. In someembodiments, one or more operations of process 1400 may be implementedin the radiation system 100 illustrated in FIG. 1. For example, theprocess 1400 may be stored in the storage device150 and/or the storage220 in the form of instructions (e.g., an application), and invokedand/or executed by the processing device 140 (e.g., the processor 210 ofthe computing device 200 as illustrated in FIG. 2, the CPU 340 of themobile device 300 as illustrated in FIG. 3, one or more modules of theprocessing device 140 as illustrated in FIG. 10, or the like). Asanother example, at least a portion of the process 1400 may beimplemented on the radiation delivery device 110. The operations of theillustrated process presented below are intended to be illustrative. Insome embodiments, the process 1400 may be accomplished with one or moreadditional operations not described, and/or without one or more of theoperations discussed. Additionally, the order in which the operations ofthe process 1400 as illustrated in FIG. 14 and described below is notintended to be limiting.

In 1410, the processing module 1030 may obtain treatment planning imagedata of the object. The treatment planning image data may refer to imagedata used to determine and/or adjust the treatment plan. In someembodiments, the treatment planning image data may be initial CT imagedata associated with the object. For example, the initial CT image datamay be obtained by the second radiation source 111 and the radiationdetector 112. As another example, the initial CT image data may beobtained by an imaging assembly outside the radiation delivery device110.

In 1420, the processing module 1030 may obtain the CT image data of theobject. The CT image data of the object may be generated by theoperation 1360 in process 1300.

In 1430, the processing module 1030 may compare the generated CT imagedata with the treatment planning image data. In some embodiments, theprocessing module 1030 may determine whether a change of the location(and/or a change of shape) of treatment region related to the object hasoccurred and/or the magnitude of such change (if any) based on thecomparison between the generated CT image data and the treatmentplanning image data. In some embodiments, the change of the locationrelated to the object may refer to a change of the location of thetreatment region (e.g., the tumor) and/or OAR, which may be caused by amovement of the object, for example, cardiac motions, respiratorymotions of the lungs and/or the diaphragm, muscle contraction andrelaxation, a displacement of the object relative to the table 115, orthe like, or a combination thereof. By comparing the generated CT imagedata with the treatment planning image data, the processing module 1030may determine the change of the location of the treatment region (e.g.,the tumor) and/or OAR. In some embodiments, both the generated CT imagedata and the treatment planning image data may be 3-dimensional (3-D)image data. Alternatively, either or both of the generated CT image dataand the treatment planning image data may be 2-dimensional (2-D) imagedata. In a case that one of the generated CT image data and thetreatment planning image is 2-D and the other one is 3-D (e.g., thegenerated CT image data is 2-D and the treatment planning image data is3-D), the treatment planning image data may be front projected togenerate 2-D treatment planning image data and compared with thegenerated CT image data which is already in 2-D.

In 1440, the processing module 1030 may determine whether the treatmentplan needs to be adjusted based on a result of the comparison. Forexample, the processing module 1030 may determine whether the change (orthe magnitude thereof) of the location of the treatment region exceeds athreshold. The threshold may be predetermined according to differentorgans and objects. In response to a result of the determination thatthe change of the location of the treatment region does not exceed athreshold, the processing module 1030 may determine that the treatmentplan does not need to be adjusted, the radiotherapy procedure maycontinue, and the process 1400 may proceed back to 1420 to obtain new CTimage data. The new CT image data may undergo the similar operations1430-1440. In response to a result of the determination that the changeof the location of the treatment region exceeds a threshold, theprocessing module 1030 may determine that the treatment plan needs to beadjusted, and the process 1400 may proceed to 1450.

In 1450, the control module 1020 may pause or stop the emission of theplurality of radiation beams from the first radiation source. In someembodiments, when the emission of the radiation beam(s) from the firstradiation source is paused or stopped, the control module 1020 may causethe first radiation source to stop rotating or rotate at a lowerrotation speed. The processing module 1030 may adjust at least some ofthe parameters associated with the treatment plan based on the CT imagedata obtained in 1420 (and/or the comparison between the CT image dataand the treatment planning image data). In some embodiments, some of theparameters associated with the radiation segments may be adjusted whileothers may remain the same. For example, if a change of shape of thetreatment region is identified while the location of the treatmentregion and the center thereof remain unchanged, only the segment shapesof the radiation segments in the treatment plan may be adjusted whileother parameters may not be adjusted.

After the adjustment to the treatment plan, the radiation deliverydevice may be controlled to work again, at a normal or reduced rotationspeed and/or radiation intensity. In some embodiments, the adjustedtreatment plan may replace the previous treatment plan and may be usedin the rotations after the adjustment. Alternatively, the adjustedtreatment plan is only used in a number of rotations, and the originaltreatment plan for the rotations after is then used.

FIG. 15 is a flowchart illustrating an exemplary process for adjustingone or more components of the radiation system based on the adjustedtreatment plan. In some embodiments, one or more operations of process1500 may be implemented in the radiation system 100 illustrated inFIG. 1. For example, the process 1500 may be stored in the storagedevice 150 and/or the storage 220 in the form of instructions (e.g., anapplication), and invoked and/or executed by the processing device 140(e.g., the processor 210 of the computing device 200 as illustrated inFIG. 2, the CPU 340 of the mobile device 300 as illustrated in FIG. 3,one or more modules of the processing device 140 as illustrated in FIG.10, or the like). As another example, at least a portion of the process1500 may be implemented on the radiation delivery device 110. Theoperations of the illustrated process presented below are intended to beillustrative. In some embodiments, the process 1500 may be accomplishedwith one or more additional operations not described, and/or without oneor more of the operations discussed. Additionally, the order in whichthe operations of the process 1500 as illustrated in FIG. 15 anddescribed below is not intended to be limiting.

In 1510, the processing module 1030 may obtain an adjusted treatmentplan. The adjusted treatment plan may be generated from operation 1450of process 1400 described above. The adjusted treatment plan may includeparameters associated with one or more radiation segments, whichincludes a desired (or an adjusted) segment shape, a desired (or anadjusted) segment intensity (e.g., a desired segment MU value, a desiredsegment MU rate), a desired (or an adjusted) segment angle range, and/ora desired (or an adjusted) relative position of the object relative tothe rotary ring.

In 1520, the processing module 1030 may move the MLC according to thedesired segment shape when a desired (or an adjusted) segment anglerange is reached during the rotation of the rotary ring. For example,the processing module 1030 may determine a desired (or an adjusted)movement of each of the leaves in the MLC based on the desired (or anadjusted) segment shape and the current shape of the aperture. Theprocessing module 1030 may send an instruction including the desired (oran adjusted) movement of each of the leaves in the MLC to acorresponding motor (e.g., motors 830) to move the leave such that theaperture formed by the moved leaves in the MLC satisfy the desired (oran adjusted) segment shape.

In 1530, the processing module 1030 may control the emission of thefirst beam and/or the second beam from the first radiation source and/orthe second radiation source based on the desired (or an adjusted)segment intensity (e.g., a desired segment MU value, a desired segmentMU rate). For example, the processing module 1030 may control thevoltage or current supply of the first radiation source and/or thesecond radiation source to control the emission of the first beam and/orthe second beam.

In 1540, the processing module 1030 may move the bed based on thedesired (or an adjusted) relative position of the object relative to therotary ring. For example, the processing module 1030 may determine adesired (or an adjusted) movement of the bed in the X,Y, or theZ-direction based on the desired(or an adjusted) relative position ofthe object with respect to the rotary ring and the current relativeposition of the object with respect to the rotary ring and send aninstruction including the desired (or an adjusted) movement in the X, Y,or the Z-direction to a motor of the bed.

In some embodiments, the radiation detector (e.g., radiation detector112, radiation detector 420, radiation detector 720) is disposed so asto receive substantially radiation originating from the second radiationsource (e.g., second radiation source 111, imaging radiation source 410,imaging radiation 710) is a CT detector. CT detectors are normallydesigned to be used with helical scanning systems in which an imagingradiation source moves relative to an imaged object along the long axisof the object. In most cases, the imaged object is a patient, and thelong axis is the head-foot axis. In most cases, the bed is moved alongthe long axis to produce the relative motion. The reason a helical scanis used is that most CT detectors have limited axial extent. In order toachieve a sufficient axial field-of-view, relative motion is usuallynecessary. When performing imaging during the treatment fraction, inmany cases it is necessary to move the bed (e.g., in a first direction)to achieve sufficient axial field-of-view. However, this motion willalso displace the treatment field with respect to the expected position.Thus, a treatment plan associated with the radiation system 100 may beadjusted to account for the motion of the treatment field. Theadjustment of the treatment plan may be found in 1370 in FIG. 13 and/or1450 in FIG. 14. If the treatment plan is not adjusted to account forthis motion, since collimator elements such as jaws and MLC leaves may,in many cases, be too slow to efficiently account for bed motion, theprocessing module 1030 may dispose the first radiation source to move ina direction along the moving direction of the bed, so that the need toaccount for bed motion by collimator motion is reduced or obviated. Thefirst radiation source may move at a speed equal to the speed of thebed. Alternatively, the 2-D MLC may be disposed to move in a directionalong the moving direction of the bed. The 2-D MLC may move at a speedequal to the moving speed of the bed. Almost all 2-D MLCs include acarriage that can simultaneously move a bank of leaves along thedirection of leaf travel. To achieve the desired relative motion whenthe direction of leaf travel is oriented along the plane of rotation, acarriage may be needed to move the leaves along the axial direction(direction of the bed).

In some embodiments, images generated by the second radiation source maybe used to modify the position of the object with respect to the firstradiation source such that a target tissue (e.g., a tumor) in the firstregion is centered at the isocenter of the radiation system 100. Theisocenter of the radiation system 100 may be a rotational isocenter,which refers to the central point of the bore (e.g., the bore 117, thebore 480) or the point that is continuously passed by the firstradiation beam emitted from the first radiation source when the rotaryring (e.g., the rotary ring 114, the rotary ring 440, the rotary ring630, the rotary ring 740) is rotating. Alternatively, the respirationinformation obtained in 1210 in FIG. 12) may be used to modify theposition of the object with respect to the first radiation source suchthat a target tissue in the first region is substantially centered atthe rotational isocenter of the radiation system 100.

In many radiation therapy cases, the target tissue of the first regionmay be partitioned into one or more subvolumes that may be treatedserially from many angles of beam incidence (during different rotationangles of the rotary ring). The processing module 1030 may be furtherconfigured to adjust a position of at least one of the subvolumes suchthat a center of the at least one of the subvolumes substantiallyoverlaps with the isocenter of the radiation system 100. For example, atumor that is substantially spherical, or contains a substantiallyspherical core subvolume may present as a target that requires littlecollimator adjustment as a function of beam incidence angle, providingthe subvolume is centered at the rotational isocenter of the treatmentsystem. In some embodiments, an imaging feedback provided by theradiation system 100 described here may be used to adjust the positionof the tumor (or target volume/subvolume) relative to the treatmentsource in such a way as to position this volume (or subvolume) of thetumor at the rotational isocenter, in order to reduce the collimatormotion required. Such an arrangement can increase treatment efficiencyespecially in cases where collimator speed (usually MLC leaf speed, inthe case of 2-D MLCs, which are MLCs that shape a cone beam into a 2-Dradiation field) is the limiting factor in treatment delivery speed. MLCspeed is likely the limiting factor in contemporary therapy systemscapable of fast gantry rotation (>2 rotations/minute) and high radiationoutput rates (>300 MU/min).

In most implementations of arc therapy systems, slow rotation speeds (<2rotations/min) are employed, and treatments are delivered using 1 or 2rotations. In order to obtain frequently updated images of tissuesduring treatment, larger rotation rates are favored. In someembodiments, the advantage of decomposing the treatment into subvolumes,such as those described above, and serially addressing such subvolumesas described above, may include preventing collimator speed limitationsfrom reducing beam-on duty cycle and overall treatment efficiency.

We have described embodiments of systems for simultaneous imaging andradiation therapy. In the context of a pulsed, and variable-duty-cycleradiation delivery and imaging system (e.g., the radiation system 100),the term “simultaneous” requires disambiguation. Linear acceleratorsources (e.g., the first radiation source 113 and the second radiationsource 111) typically produce pulses with duty cycles (e.g., a ratiobetween a on-period and a off-period) of the order of 1:1000. For thevast majority of time during a treatment session when the beam isconsidered “on”, no radiation is being produced. It is possible to imageduring the off-period. Such imaging is still regarded as occurringsimultaneously with the treatment. This is because the treatment hasalready commenced, and will continue within a time period that is veryshort. There may be periods of the order 1-10,000 ms, between parts ofthe treatment delivery, where the treatment source is switched off orcollimated off. Imaging that occurs during this time, as well as imagingthat occurs while the treatment beam is on, are both regarded as imagingthat is simultaneous with treatment. In contrast, imaging that occursafter the treatment beam has been off (i.e., is not impartingsubstantial dose to the patient) for more than a complete systemrotation, and imaging that occurs more than 10 s after the treatmentbeam has been turned off, is not regarded, for the purposes of theteachings contained herein, as imaging that is simultaneous with thetreatment.

Having thus described the basic concepts, it may be rather apparent tothose skilled in the art after reading this detailed disclosure that theforegoing detailed disclosure is intended to be presented by way ofexample only and is not limiting. Various alterations, improvements, andmodifications may occur and are intended to those skilled in the art,though not expressly stated herein. These alterations, improvements, andmodifications are intended to be suggested by this disclosure and arewithin the spirit and scope of the exemplary embodiments of thisdisclosure.

Moreover, certain terminology has been used to describe embodiments ofthe present disclosure. For example, the terms “one embodiment,” “anembodiment,” and/or “some embodiments” mean that a particular feature,structure or characteristic described in connection with the embodimentis included in at least one embodiment of the present disclosure.Therefore, it is emphasized and should be appreciated that two or morereferences to “an embodiment” or “one embodiment” or “an alternativeembodiment” in various portions of this specification are notnecessarily all referring to the same embodiment. Furthermore, theparticular features, structures or characteristics may be combined assuitable in one or more embodiments of the present disclosure.

Further, it will be appreciated by one skilled in the art, aspects ofthe present disclosure may be illustrated and described herein in any ofa number of patentable classes or context including any new and usefulprocess, machine, manufacture, or composition of matter, or any new anduseful improvement thereof. Accordingly, aspects of the presentdisclosure may be implemented entirely hardware, entirely software(including firmware, resident software, micro-code, etc.) or combiningsoftware and hardware implementation that may all generally be referredto herein as a “unit,” “module,” or “system.” Furthermore, aspects ofthe present disclosure may take the form of a computer program productembodied in one or more computer-readable media having computer readableprogram code embodied thereon.

A computer readable signal medium may include a propagated data signalwith computer readable program code embodied therein, for example, inbaseband or as part of a carrier wave. Such a propagated signal may takeany of a variety of forms, including electromagnetic, optical, or thelike, or any suitable combination thereof. A computer readable signalmedium may be any computer readable medium that is not a computerreadable storage medium and that may communicate, propagate, ortransport a program for use by or in connection with an instructionexecution system, apparatus, or device. Program code embodied on acomputer readable signal medium may be transmitted using any appropriatemedium, including wireless, wireline, optical fiber cable, RF, or thelike, or any suitable combination of the foregoing.

Computer program code for carrying out operations for aspects of thepresent disclosure may be written in a combination of one or moreprogramming languages, including an object-oriented programming languagesuch as Java, Scala, Smalltalk, Eiffel, JADE, Emerald, C++, C#, VB. NET,Python or the like, conventional procedural programming languages, suchas the “C” programming language, Visual Basic, Fortran 2103, Perl, COBOL2102, PHP, ABAP, dynamic programming languages such as Python, Ruby, andGroovy, or other programming languages. The program code may executeentirely on the user's computer, partly on the user's computer, as astand-alone software package, partly on the user's computer and partlyon a remote computer or entirely on the remote computer or server. Inthe latter scenario, the remote computer may be connected to the user'scomputer through any type of network, including a local area network(LAN) or a wide area network (WAN), or the connection may be made to anexternal computer (for example, through the Internet using an InternetService Provider) or in a cloud computing environment or offered as aservice such as a Software as a Service (SaaS).

Furthermore, the recited order of processing elements or sequences, orthe use of numbers, letters, or other designations, therefore, is notintended to limit the claimed processes and methods to any order exceptas may be specified in the claims. Although the above disclosurediscusses through various examples what is currently considered to be avariety of useful embodiments of the disclosure, it is to be understoodthat such detail is solely for that purpose and that the appended claimsare not limited to the disclosed embodiments, but, on the contrary, areintended to cover modifications and equivalent arrangements that arewithin the spirit and scope of the disclosed embodiments. For example,although the implementation of various components described above may beembodied in a hardware device, it may also be implemented as asoftware-only solution, for example, an installation on an existingserver or mobile device.

Similarly, it should be appreciated that in the foregoing description ofembodiments of the present disclosure, various features are sometimesgrouped in a single embodiment, figure, or descriptions thereof for thepurpose of streamlining the disclosure aiding in the understanding ofone or more of the various inventive embodiments. This method ofdisclosure, however, is not to be interpreted as reflecting an intentionthat the claimed subject matter requires more features than areexpressly recited in each claim. Rather, inventive embodiments lie inless than all features of a single foregoing disclosed embodiment.

In some embodiments, the numbers expressing quantities or propertiesused to describe and claim certain embodiments of the application are tobe understood as being modified in some instances by the term “about,”“approximate,” or “substantially.” For example, “about,” “approximate,”or “substantially” may indicate ±20% variation of the value itdescribes, unless otherwise stated. Accordingly, in some embodiments,the numerical parameters set forth in the written description andattached claims are approximations that may vary depending upon thedesired properties sought to be obtained by a particular embodiment. Insome embodiments, the numerical parameters should be construed in lightof the number of reported significant digits and by applying ordinaryrounding techniques. Notwithstanding that the numerical ranges andparameters setting forth the broad scope of some embodiments of theapplication are approximations, the numerical values set forth in thespecific examples are reported as precisely as practicable.

Each of the patents, patent applications, publications of patentapplications, and other material, such as articles, books,specifications, publications, documents, things, and/or the like,referenced herein is hereby incorporated herein by this reference in itsentirety for all purposes, excepting any prosecution file historyassociated with same, any of same that is inconsistent with or inconflict with the present document, or any of same that may have alimiting affect as to the broadest scope of the claims now or laterassociated with the present document. By way of example, should there beany inconsistency or conflict between the description, definition,and/or the use of a term associated with any of the incorporatedmaterial and that associated with the present document, the description,definition, and/or the use of the term in the present document shallprevail.

In closing, it is to be understood that the embodiments of theapplication disclosed herein are illustrative of the principles of theembodiments of the application. Other modifications that may be employedmay be within the scope of the application. Thus, by way of example, butnot of limitation, alternative configurations of the embodiments of theapplication may be utilized in accordance with the teachings herein.Accordingly, embodiments of the present application are not limited tothat precisely as shown and described.

What is claimed is:
 1. A radiation system, comprising: a bore configuredto accommodate an object; a rotary ring; a first radiation sourcemounted on the rotary ring and configured to emit a first cone beamtoward a first region of the object; a second radiation source mountedon the rotary ring and configured to emit a second beam toward a secondregion of the object, the second region including at least a part of thefirst region; and a processor configured to cause the radiation systemto: obtain a treatment plan of the object, the treatment plan includingone or more radiation segments; cause the rotary ring to rotate aroundthe object in one direction continuously for at least two fullrotations; and control an emission of at least one of the first conebeam or the second beam based on the treatment plan to perform atreatment and a 3-D imaging simultaneously.
 2. The radiation system ofclaim 1, wherein the processor is further configured to cause theradiation system to: obtain respiration information of the object;determine a rotation parameter of the rotary ring based on therespiration information of the object; and control a rotation of therotary ring based at least in part on the rotation parameter.
 3. Theradiation system of claim 2, wherein the respiration informationincludes an average respiration period, a minimum respiration period, ora maximum respiration period.
 4. The radiation system of claim 1,wherein a period that the rotary ring rotates a full rotation is notmore than half of an average respiration period of the object.
 5. Theradiation system of claim 1, wherein a period that the rotary ringrotates a full rotation is less than 30 seconds.
 6. The radiation systemof claim 1, wherein an angular offset between the first radiation sourceand the second radiation source in a rotation plane of the rotary ringremains unchanged during the rotation of the rotary ring.
 7. Thradiation system of claim 1, wherein the first cone beam and the secondbeam are emitted in a same full rotation of the rotary ring.
 8. Theradiation system of claim 1, wherein the first cone beam and the secondbeam are emitted in a same fraction of a full rotation of the rotaryring.
 9. The radiation system of claim 1, wherein a cone angle of thesecond beam is greater than or equal to a cone angle of the first conebeam.
 10. The radiation system of claim 1, wherein shapes and/orintensities of the first cone beam in different radiation segments aredifferent.
 11. The radiation system of claim 1, further comprising acollimator positioned between a center of the bore and the firstradiation source to form at least one aperture, wherein the processor isfurther configured to cause the radiation system to: adjust the at leastone aperture of the collimator based on the treatment plan.
 12. Theradiation system of claim 11, wherein the treatment plan includes adesired segment shape of at least one of the one or more radiationsegments, and the at least one aperture is adjusted to modify a shape ofthe first cone beam to match the desired segment shape.
 13. Theradiation system of claim 11, wherein to adjust the at least oneaperture of the collimator based on the treatment plan, the at theprocessor is further configured to cause the radiation system to: adjustthe at least one aperture of the collimator during an interval betweentwo radiation segments.
 14. The radiation system of claim 1, furthercomprising a radiation detector configured to detect radiation impingingon the radiation detector, wherein the processor is further configuredto cause the radiation system to: obtain treatment planning image dataof the object associated with the treatment plan; generate CT image databased on the radiation detected by the radiation detector, the detectedradiation being associated with at least one of the first cone beam orthe second beam; compare the generated CT image data with the treatmentplanning image data; and adjust at least part of the treatment planbased on a comparison result.
 15. The radiation system of claim 1,further comprising a radiation detector configured to detect radiationimpinging on the detector, wherein the processor is further configuredto cause the radiation system to: cause the rotary ring to rotate afirst full rotation; adjust parameters associated with the one or moreradiation segments at which the first radiation source emits the firstcone beam in a second full rotation based on radiation detected by theradiation detector in the first full rotation, the second full rotationbeing after the first full rotation; and control an emission of thefirst cone beam based on the adjusted parameters associated with the oneor more radiation segments.
 16. The radiation system of claim 15,wherein the processor is further configured to cause the radiationsystem to: move the first radiation source or a collimator positionedbetween a center of the bore and the first radiation source to reduce oreliminate a displacement between the first radiation source and theobject before or during the second full rotation.
 17. The radiationsystem of claim 1, further comprising a bed configured to support theobject, wherein the processor is further configured to cause theradiation system to: adjust a position of the bed based on a desiredposition of the object included in the treatment plan with respect tothe rotary ring.
 18. The radiation system of claim 1, further comprisinga bed configured to support the object, wherein the processor is furtherconfigured to cause the radiation system to: move the first radiationsource in a direction the same as that of the bed during the rotation ofthe rotation ring, a moving speed of the first radiation source beingequal to that of the bed.
 19. The radiation system of claim 1, whereinthe at least one processor is configured to cause the system to: modifya position of the object with respect to the first radiation sourcebased on an image generated by the second radiation source such that atarget tissue of the object is centered at an isocenter of the radiationsystem.
 20. The radiation system of claim 1, wherein to perform the 3-Dimaging, the at least one processor is configured to cause the systemto: generate a 3-D image based on a received radiation associated withat least one of the first cone beam and the second beam.